Bone regeneration using biodegradable polymeric nanocomposite materials and applications of the same

ABSTRACT

A biocompatible structure includes one or more base structures for regeneration of different tissues. Each base structure includes alternately stacked polymer layers and spacer layers. The polymer layer includes a polymer and tissue forming nanoparticles. The polymer includes polyurethane. The tissue forming nanoparticles includes hydroxypatites (HAP) nanoparticles, polymeric nanoparticles, or nanofibers. The spacer layer includes bone particles, polymeric nanoparticles, or nanofibers. The weight percentage of tissue forming nanoparticles to the polymer in the polymer layer in one base structure is different from that in the other base structures. A method of producing the biocompatible structure includes forming multiple base structures stacked together, coating the stacked multiple base structures, and plasma treating the coated structure.

CROSS-REFERENCE TO RELATED PATENT APPLICATION

This application is a divisional application of, and claims benefit ofU.S. patent application Ser. No. 14/509,719, filed Oct. 8, 2014,entitled “BONE REGENERATION USING BIODEGRADABLE POLYMERIC NANOCOMPOSITEMATERIALS AND APPLICATIONS OF THE SAME”, by Alexandru S. Bilis, nowallowed, which is incorporated herein by reference in its entirety.

Some references, which may include patents, patent applications andvarious publications, are cited and discussed in the description of thisdisclosure. The citation and/or discussion of such references isprovided merely to clarify the description of the present disclosure andis not an admission that any such reference is “prior art” to thedisclosure described herein. All references cited and discussed in thisspecification are incorporated herein by reference in their entiretiesand to the same extent as if each reference was individuallyincorporated by reference.

STATEMENT OF FEDERALLY-SPONSORED RESEARCH

This disclosure was made with Government support under Grant No.W81XWH-10-2-0130 awarded by the U.S. Department of Defense. TheGovernment has certain rights in the disclosure.

FIELD

The present disclosure relates generally to a biocompatible structurehaving one or more base structures for bone and tissue regeneration, andmore particularly to a biodegradable and bioresorbable nanocompositeincorporating polymer, nanostructured hydroxyapatite and optionallyother beneficial factors.

BACKGROUND

The background description provided herein is for the purpose ofgenerally presenting the context of the disclosure. Work of thepresently named inventors, to the extent it is described in thisbackground section, as well as aspects of the description that may nototherwise qualify as prior art at the time of filing, are neitherexpressly nor impliedly admitted as prior art against the presentdisclosure.

Skeletal deficiencies from trauma, tumors and bone diseases, or abnormaldevelopment frequently require surgical procedures to attempt to restorenormal bone function. Although most of these treatments are successful,they all have problems and limitations.

Therefore, a heretofore unaddressed need exists in the art to addressthe aforementioned deficiencies and inadequacies.

SUMMARY

Certain aspects of the present disclosure are directed to an implantincluding two or more biocompatible structures. Each of thebiocompatible structures is biodegradable and bioresorbable.

In one aspect, the present disclosure is directed to a method ofproducing a biocompatible structure for bone and tissue regeneration.The method includes: forming multiple first polymer layers by:dissolving a first polymer in a first solvent to form a first solution;adding first tissue forming nanoparticles to the first solution to forma second solution, where a first weight percentage of the first tissueforming nanoparticles to the first polymer is about 0.01-95%; applyingthe second solution to a first surface to form a first polymer film onthe first surface, where the first tissue forming nanoparticles aredispersed in the first polymer film; and dividing the first polymer filminto the multiple first polymer layers;

forming multiple second polymer layers by: dissolving a second polymerin a second solvent to form a third solution; adding second tissueforming nanoparticles to the third solution to form a fourth solution,where a second weight percentage of the second tissue formingnanoparticles to the second polymer is greater than the first weightpercentage; applying the fourth solution to a second surface to form asecond polymer film on the second surface, where the second tissueforming nanoparticles are dispersed in the second polymer film; anddividing the second polymer film into the multiple second polymerlayers; and

forming the biocompatible structure by the first polymer layers, firstspacer particles, the second polymer layers, second spacer particles,and a fifth solution.

In one embodiment, the formed biocompatible structure includes the firstpolymer layers, the second polymer layers, the first spacer particlesplaced between two of the first polymer layers, and the second spacerparticles placed between two of the second polymer layers.

In one embodiment, the fifth solution includes at least one of the firstand the second tissue forming particles, at least one of the firstpolymer and the second polymer, and at least one of the first solventand the second solvent.

In one embodiment, the step of forming the multiple first polymer layersfurther includes: stirring the first solution to uniformly distributethe first polymer in the first solution; sonicating the second solutionto uniformly distribute the first polymer and the first tissue formingnanoparticles in the second solution; and drying the second solution onthe first surface to form the first polymer film on the first surface.

In one embodiment, the step of forming the multiple second polymerlayers further includes: stirring the third solution to uniformlydistribute the second polymer in the third solution; sonicating thefourth solution to uniformly distribute the second polymer and thesecond tissue forming nanoparticles in the fourth solution; and dryingthe fourth solution on the second surface to form the second polymerfilm on the second surface.

In one embodiment, the step of forming the biocompatible structureincludes: constructing a first base structure by stacking the firstpolymer layers and first spacer layers alternatively, wherein each ofthe first spacer layers is formed by the first spacer particles;constructing a second base structure on the first base structure bystacking the second polymer layers and second spacer layersalternatively, wherein each of the second spacer layers is formed by thesecond spacer particles; applying the fifth solution to the first basestructure and the second base structure to form a coated structure; andadding third spacer particles to the coated structure to form thebiocompatible structure.

In one embodiment, after adding the third spacer particles to the coatedstructure, further including plasma treating the coated structure. Theplasma treating may be a nitrogen or oxygen plasma treating.

In one embodiment, at least one of the first polymer layers, the secondpolymer layers, the first base structure, the second base structure, andthe biocompatible structure is manufactured by 3D printing or layer bylayer 2D printing.

In one embodiment, at least one of a thickness of the first polymerlayer, a distance between two neighboring first polymer layers, athickness of the first spacer layer, a porosity of the first spacerparticles is different from a thickness of the second polymer layer, adistance between two neighboring second polymer layers, a thickness ofthe first spacer layer, a porosity of the second spacer particles,respectively, such that when being applied to an implant site, each ofthe first and the second base structure corresponds to a type of tissuein the implant site, and facilitates regeneration of the correspondingtissue.

In one embodiment, a degradation rate of the first base structure isslower than a degradation rage of the second base structure.

In one embodiment, each of the first and the second base structures hasa size and shape conforming to a size and shape of corresponding tissueof an implant site.

In one embodiment, the first polymer is the same as the second polymer,the first tissue forming nanoparticles are different from the secondtissue forming nanoparticles, the first solvent is the same as thesecond solvent, the first weight percentage is about 15-30%, and thesecond weight percentage is about 10-25%.

In one embodiment, the first polymer is the same as the second polymer,the first tissue forming nanoparticles are the same as the second tissueforming nanoparticles, the first solvent is the same as the secondsolvent, the first weight percentage is about 15-30%, and the secondweight percentage is about 10-25%.

In one embodiment, the first weight percentage is about 17-23%, and thesecond weight percentage is about 15-20%.

In one embodiment, the first weight percentage is about 25%, and thesecond weight percentage is about 22%.

In one embodiment, each of the first and second polymer includes asynthetic biodegradable polymer, a biodegradable polymer derived fromnatural source, or a mixture thereof. The synthetic biodegradablepolymer includes polyurethane, polylactide (PLA), polyglycolide (PGA),poly(lactide-co-glycolide) (PLGA), poly(e-caprolactone), polydioxanone,polyanhydride, trimethylene carbonate, poly((3-hydroxybutyrate),poly(g-ethyl glutamate), poly(DTH iminocarbonate), poly(bisphenol Aiminocarbonate), poly(ortho ester), polycyanoacrylate, polyphosphazene,or a mixture thereof. The biodegradable polymer derived from naturalsource includes modified polysaccharides, modified proteins, or amixture thereof. Each of the first and second tissue formingnanoparticles includes nanoparticles of hydroxypatites, tricalciumphosphates, mixed calcium phosphates and calcium carbonate, boneparticles of zenograft, bone particles of allografts, bone particles ofautografts, bone particles of alloplastic grafts, polymericnanoparticles, nanofibers, or a mixture thereof. The surface is apolytetrafluoroethylene (PTFE) surface. The second tissue formingparticles includes nano-sized bone particles, micro-sized boneparticles, or a mixture thereof.

In one embodiment, the method further includes adding a third tissueforming material to the biocompatible structure. The third tissueforming material includes a bioactive material, cells, or a mixturethereof. The bioactive material includes proteins, enzymes, growthfactors, amino acids, bone morphogenic proteins, platelet derived growthfactors, vascular endothelial growth factors, or a mixture thereof. Thecells includes epithelial cells, neurons, glial cells, astrocytes,podocytes, mammary epithelial cells, islet cells, endothelial cells,mesenchymal cells, stem cells, osteoblast, muscle cells, striated musclecells, fibroblasts, hepatocytes, ligament fibroblasts, tendonfibroblasts, chondrocytes, or a mixture thereof. In one embodiment, thecells include stem cells, bone cells or the cells required for theparticular tissue.

In one embodiment, at least one of the first polymer layers and thesecond polymer layers has a length of about 0.005-50 centimeter, a widthof about 0.002-50 centimeter, and a thickness of about 0.001-500millimeter, and each of the first base structure and the second basestructure is in a cylindrical shape or a spherical shape.

In one aspect, the present disclosure is directed to a method ofproducing a biocompatible structure for bone and tissue regeneration. Incertain embodiments, the biocompatible structure includes a first basestructure, a second base structure, and a coating. Each of the firstbase structure and the second base structure includes a plurality ofpolymeric layers and a plurality of demineralized bone componentparticle layers. In one embodiment, the polymeric layers and thedemineralized bone component particle layers are stacked alternately.The coating covers the first base structure and the second basestructure. The method includes depositing each of the polymeric layersby air spray deposition, electrospray, droplet by droplet deposition, 2Dprinting, or 3D printing of a first solution comprising a polymer and asolvent, and depositing each of the demineralized bone componentparticle layers by electrostatic deposition or air spray of a secondsolution comprising demineralized bone component particles and thesolvent.

In one aspect, the present disclosure is directed to a biocompatiblestructure. In one embodiment, the biocompatible structure includes afirst base structure, a second base structure disposed on the first basestructure, a coating surrounding the first base structure and the secondbase structure; and multiple third spacer particles attached to an outersurface of the coating.

In one embodiment, the first base structure includes multiple firstpolymer layers and multiple first spacer layers disposed between each ofthe two neighboring first polymer layers. The multiple first polymerlayers are stacked to have a predetermined shape. Each of the firstpolymer layers is formed with a first polymer and first tissue formingnanoparticles. A first weight percentage of the first tissue formingnanoparticles to the first polymer layer is in a range of about 0.5-95%.Each of the first spacer layers includes first spacer particles.

In one embodiment, the second base structure includes multiple secondpolymer layers and multiple second spacer particle layers disposedbetween each of the two neighboring second polymer layers. The multiplesecond polymer layers are stacked to have a predetermined shape. Each ofthe second polymer layers is formed with a second polymer and a secondtissue forming nanoparticles. A second weight percentage of the secondtissue forming nanoparticles to the second polymer layer is in a rangeof about 0.5-95%. The first weight percentage is greater than the secondweight percentage. Each of the second spacer layers includes secondspacer particles.

In one embodiment, the first polymer is the same as the second polymer,the first tissue forming nanoparticles are HAP nanoparticles, the secondtissue forming nanoparticles are nanofibers, the first weight percentageis about 15-30%, and the second weight percentage is about 10-25%.

In one embodiment, the first polymer is the same as the second polymer,the first tissue forming nanoparticles are the same as the second tissueforming nanoparticles, the first spacer particles and the second spacerparticles are the same as the third spacer particles, the first weightpercentage is about 15-30%, and the second weight percentage is about10-25%.

In one embodiment, the first weight percentage is about 17-23%, thesecond weight percentage is about 15-20%.

In one embodiment, the first weight percentage is about 20%, the secondweight percentage is about 18%.

In one embodiment, at least one of a thickness of the first polymerlayer, a distance between two neighboring first polymer layers, athickness of the first spacer layer, a porosity of the first spacerparticles is different from a thickness of the second polymer layer, adistance between two neighboring second polymer layers, a thickness ofthe first spacer layer, a porosity of the second spacer particles,respectively, such that when being applied to an implant site, each ofthe first and the second base structure corresponds to a type of tissuein the implant site, and aids regeneration of the corresponding tissue.

In one embodiment, the distance between two neighboring first polymerlayers is greater than the distance between two neighboring secondpolymer layers.

In one embodiment, the density of the first spacer particles in thefirst spacer layers is greater than the density of the second spacerparticles in the second spacer layers.

In one embodiment, a degradation rate of the first base structure isslower than a degradation rage of the second base structure.

In one embodiment, each of the first base structure and the second basestructure of the biocompatible structure has a size and shape conformingto a size and shape of the corresponding tissue of the implant site.

In one embodiment, each of the first polymer and the second polymerincludes a synthetic biodegradable polymer, a biodegradable polymerderived from natural source, or a mixture thereof.

In one embodiment, the synthetic biodegradable polymer includespolyurethane, polylactide (PLA), polyglycolide (PGA),poly(lactide-co-glycolide) (PLGA), poly(e-caprolactone), polydioxanone,polyanhydride, trimethylene carbonate, poly((3-hydroxybutyrate),poly(g-ethyl glutamate), poly(DTH iminocarbonate), poly(bisphenol Aiminocarbonate), poly(ortho ester), polycyanoacrylate, polyphosphazene,or a mixture thereof.

In one embodiment, the biodegradable polymer derived from natural sourceincludes modified polysaccharides, modified proteins, or a mixturethereof;

In one embodiment, each of the first and second tissue formingnanoparticles includes nanoparticles of hydroxypatites (HAP), tricalciumphosphates, mixed calcium phosphates and calcium carbonate, boneparticles of zenograft, bone particles of allografts, bone particles ofautografts, bone particles of alloplastic grafts, polymericnanoparticles, nanofibers, or a mixture thereof.

In one embodiment, each of the first spacer particles, the second spacerparticles, and the third spacer particles includes nano-sized boneparticles, micro-sized bone particles, polymeric nanoparticles,nanofibers, or a mixture thereof.

In one embodiment, the first spacer particles are bone particles, andthe second spacer particles are polymeric nanoparticles or polymericnanofibers.

In one embodiment, the biocompatible structure further includes a thirdtissue forming material.

In one embodiment, the third tissue forming material includes abioactive material, cells, or a mixture thereof.

In one embodiment, the bioactive material includes proteins, enzymes,growth factors, amino acids, bone morphogenic proteins, platelet derivedgrowth factors, vascular endothelial growth factors, or a mixturethereof.

In one embodiment, the cells includes epithelial cells, neurons, glialcells, astrocytes, podocytes, mammary epithelial cells, islet cells,endothelial cells, mesenchymal cells, stem cells, osteoblast, musclecells, striated muscle cells, fibroblasts, hepatocytes, ligamentfibroblasts, tendon fibroblasts, chondrocytes, or a mixture thereof.

In one embodiment, at least one of the first and second polymer layershas a length of about 0.05-200 centimeter, a width of about 0.02-50centimeter, and a thickness of about 0.01-500 millimeter, and each ofthe first and the second scaffold is in a cylindrical shape, rectangularshape or a spherical shape.

In one embodiment, the biocompatible structure of claim is plasmatreated. The plasma treating may be a nitrogen or oxygen plasmatreating.

Certain aspects of the present disclosure are directed to a method oftreating bone deficiencies. The method includes applying an implant toan implant surgical site. The implant includes one or more biocompatiblestructures. The biocompatible structure includes polymer layers stackedto have a predetermined shape, bone particle layers disposed betweeneach of the two neighboring polymer layers; a coating surrounding thepolymer layers and bone particle layers; and bone particles attached toan outer surface of the coating. Each of the polymer layers is formedwith a polymer and first tissue forming nanoparticles. The implantsurgical site can have deficiencies of different tissues. Thepredetermined shape of each biocompatible structure in the implant isconfigured to conform to a corresponding tissue of the implant surgicalsite. A weight percentage of the first tissue forming nanoparticles tothe polymer is about 5-50% such that a resorption rate of thebiocompatible structure substantially matches a rate of tissuegeneration in the biocompatible structure.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings illustrate one or more embodiments of thedisclosure and, together with the written description, serve to explainthe principles of the disclosure. The same reference numbers may be usedthroughout the drawings to refer to the same or like elements in theembodiments.

FIG. 1A illustrates a biocompatible structure according to certainembodiments of the present disclosure.

FIG. 1B illustrates a biocompatible structure inserted into an implantsurgical site according to certain embodiments of the presentdisclosure.

FIG. 1C illustrates an enlarged view of a part circled in FIG. 1B.

FIG. 2A illustrates a biocompatible structure having two base structuresaccording to certain embodiments of the present disclosure.

FIG. 2B illustrates base structures of the biocompatible structureaccording to certain embodiments of the present disclosure.

FIG. 2C illustrates a part of a base structure of the biocompatiblestructure according to certain embodiments of the present disclosure.

FIG. 3A illustrates a biocompatible structure having one base structureaccording to certain embodiments of the present disclosure.

FIG. 3B schematically shows a Scanning Electron Microscopy image of abiocompatible structure at a low resolution according to certainembodiments of the present disclosure.

FIGS. 3C-3E schematically show Scanning Electron Microscopy images of abiocompatible structure at a high resolution according to certainembodiments of the present disclosure.

FIGS. 4A and 4B schematically shows procedures for producing abiocompatible structure having two base structures according to certainembodiments of the present disclosure.

FIG. 5 schematically shows procedures for producing a biocompatiblestructure having two base structure according to certain embodiments ofthe present disclosure.

FIG. 6 schematically shows procedures for producing a biocompatiblestructure having two base structures according to certain embodiments ofthe present disclosure.

FIGS. 7A and 7B schematically show a pull test set up for measuringmaximum load and maximum stress of polymer films according to certainembodiments of the present disclosure.

FIG. 8 schematically shows maximum load of the polymer films accordingto certain embodiments of the present disclosure.

FIG. 9 schematically shows maximum stress of the polymer films accordingto certain embodiments of the present disclosure.

DETAILED DESCRIPTION

The disclosure will now be described more fully hereinafter withreference to the accompanying drawings, in which exemplary embodimentsof the disclosure are shown. This invention may, however, be embodied inmany different forms and should not be construed as limited to theembodiments set forth herein. Rather, these embodiments are provided sothat this disclosure will be thorough and complete, and will fullyconvey the scope of the disclosure to those skilled in the art. Likereference numerals refer to like elements throughout.

The terms used in this specification generally have their ordinarymeanings in the art, within the context of the disclosure, and in thespecific context where each term is used. Certain terms that are used todescribe the disclosure are discussed below, or elsewhere in thespecification, to provide additional guidance to the practitionerregarding the description of the disclosure. For convenience, certainterms may be highlighted, for example using italics and/or quotationmarks. The use of highlighting and/or capital letters has no influenceon the scope and meaning of a term; the scope and meaning of a term arethe same, in the same context, whether or not it is highlighted and/orin capital letters. It will be appreciated that the same thing can besaid in more than one way. Consequently, alternative language andsynonyms may be used for any one or more of the terms discussed herein,nor is any special significance to be placed upon whether or not a termis elaborated or discussed herein. Synonyms for certain terms areprovided. A recital of one or more synonyms does not exclude the use ofother synonyms. The use of examples anywhere in this specification,including examples of any terms discussed herein, is illustrative onlyand in no way limits the scope and meaning of the disclosure or of anyexemplified term. Likewise, the disclosure is not limited to variousembodiments given in this specification.

It will be understood that when an element is referred to as being “on”another element, it can be directly on the other element or interveningelements may be present therebetween. In contrast, when an element isreferred to as being “directly on” another element, there are nointervening elements present. As used herein, the term “and/or” includesany and all combinations of one or more of the associated listed items.

It will be understood that, although the terms first, second, third,etc. may be used herein to describe various elements, components,regions, layers and/or sections, these elements, components, regions,layers and/or sections should not be limited by these terms. These termsare only used to distinguish one element, component, region, layer orsection from another element, component, region, layer or section. Thus,a first element, component, region, layer or section discussed below canbe termed a second element, component, region, layer or section withoutdeparting from the teachings of the disclosure.

It will be understood that when an element is referred to as being “on”,“attached” to, “connected” to, “coupled” with, “contacting”, etc.,another element, it can be directly on, attached to, connected to,coupled with or contacting the other element or intervening elements mayalso be present. In contrast, when an element is referred to as being,for example, “directly on”, “directly attached” to, “directly connected”to, “directly coupled” with or “directly contacting” another element,there are no intervening elements present.

It will also be appreciated by those of skill in the art that referencesto a structure or feature that is disposed “adjacent” to another featuremay have portions that overlap or underlie the adjacent feature.

The terminology used herein is for the purpose of describing particularembodiments only and is not intended to be limiting of the disclosure.As used herein, the singular forms “a”, “an” and “the” are intended toinclude the plural forms as well, unless the context clearly indicatesotherwise. It will be further understood that the terms “comprises”and/or “comprising”, or “includes” and/or “including” or “has” and/or“having” when used in this specification specify the presence of statedfeatures, regions, integers, steps, operations, elements, and/orcomponents, but do not preclude the presence or addition of one or moreother features, regions, integers, steps, operations, elements,components, and/or groups thereof.

Furthermore, relative terms, such as “lower” or “bottom” and “upper” or“top”, may be used herein to describe one element's relationship toanother element as illustrated in the figures. It will be understoodthat relative terms are intended to encompass different orientations ofthe device in addition to the orientation shown in the figures. Forexample, if the device in one of the figures is turned over, elementsdescribed as being on the “lower” side of other elements would then beoriented on the “upper” sides of the other elements. The exemplary term“lower” can, therefore, encompass both an orientation of lower andupper, depending on the particular orientation of the figure. Similarly,if the device in one of the figures is turned over, elements describedas “below” or “beneath” other elements would then be oriented “above”the other elements. The exemplary terms “below” or “beneath” can,therefore, encompass both an orientation of above and below.

Unless otherwise defined, all terms (including technical and scientificterms) used herein have the same meaning as commonly understood by oneof ordinary skill in the art to which this invention belongs. It will befurther understood that terms, such as those defined in commonly useddictionaries, should be interpreted as having a meaning that isconsistent with their meaning in the context of the relevant art and thepresent disclosure, and will not be interpreted in an idealized oroverly formal sense unless expressly so defined herein.

As used herein, the terms “comprise” or “comprising”, “include” or“including”, “carry” or “carrying”, “has/have” or “having”, “contain” or“containing”, “involve” or “involving” and the like are to be understoodto be open-ended, i.e., to mean including but not limited to.

As used herein, the phrase “at least one of A, B, and C” should beconstrued to mean a logical (A or B or C), using a non-exclusive logicalOR. It should be understood that one or more steps within a method maybe executed in different order (or concurrently) without altering theprinciples of the disclosure.

Typically, terms such as “about,” “approximately,” “generally,”“substantially,” and the like unless otherwise indicated mean within 20percent, preferably within 10 percent, preferably within 5 percent, andeven more preferably within 3 percent of a given value or range.Numerical quantities given herein are approximate, meaning that the term“about,” “approximately,” “generally,” or “substantially” can beinferred if not expressly stated.

Typically, “nanoscopic-scale,” “nanoscopic,” “nanometer-scale,”“nanoscale,” the “nano-” prefix, and the like refers to elements orarticles having widths or diameters of less than about 1 μm, preferablyless than about 100 nm in some cases. Specified widths can be smallestwidth (i.e. a width as specified where, at that location, the articlecan have a larger width in a different dimension), or largest width(i.e. where, at that location, the article's width is no wider than asspecified, but can have a length that is greater), unless pointed outotherwise.

In most of the tissue trauma, there is loss of more than one type oftissues in an implant surgical site of a human or an animal. Abiocompatible structure can be adapted to include multiple basestructures having different properties, thus facilitating regenerationof two or more tissues in the implant surgical site of the human or theanimal, or facilitating regeneration of tissues in a non-implantsurgical site of the human or the animal and then transferred to theimplant site, or facilitating regeneration of tissues in vitro or in thelab and then transferred to the implant surgical site. Alternatively,the biocompatible structure can have only one base structure.

FIG. 1A schematically shows structure of a biocompatible structure 90according to certain embodiments of the present disclosure. In oneembodiment as shown in FIG. 1A, the biocompatible structure 90 has twobase structures. Alternatively, the biocompatible structure 90 caninclude various number of (such as three, four, five, and six, or more)base structures. In one embodiment, the implant surgical site may have abone tissue loss and a muscle tissue loss. In certain embodiments, thebiocompatible structure 90 has a first base structure 100 and a secondbase structure 200, which have different properties for facilitatingregeneration of different tissues in the implant site.

The first base structure 100 has specific polymer layer thickness,polymer layer distance, spacer particle layer thickness, spacer particledensity, and degradation rate that allow bone regeneration in the boneloss portion of the implant surgical site. The second base structure 200has specific polymer layer thickness, polymer layer distance, spacerparticle layer thickness, spacer particle density, and degradation ratethat allow muscle regeneration in the muscle tissue loss portion of theimplant surgical site. The biocompatible structure 90 can be in anyshape that conforms to a shape of the implant site. For example, each ofthe first base structure 100 and the second base structure 200 can havea cylindrical shape, a rectangular shape, or a spherical shape. Incertain embodiments, the base structures 100 and 200 in thebiocompatible structure 90 have different properties, such as mechanicalproperties or biological properties, the mechanical properties caninclude intensity, pore density etc., and the different base structurescorrespond to different tissues in the implant surgical site. In certainembodiments, as shown in FIG. 1B and FIG. 1C, the implant surgical site50 includes a bone area 500 and a muscle area 600. Correspondingly, thebiocompatible structure 90 including the first base structure 100 andthe second base structure 200 is applied to the implant surgical site50. The size and the shape of the first base structure 100 correspond tothe size and the shape of the bone area 500, and the properties of thefirst base structure 100 is suitable for the regeneration of bone tissuein the bone area 500. For example, the base 100 can be configured tomeet the needs for the regeneration of bone tissue, can have mechanicalproperties matching the tissues to be regenerated, and can delivergrowth factors specific for bone regeneration, cells, and/or can deliverantimicrobials. The size and the shape of the second base structure 200correspond to the size and the shape of the muscle area 600, theproperties of the second base structure 200 is suitable for theregeneration of muscle in the muscle area 600, and the second basestructure 200 can carry cells and/or growth factors that are specific tothis type of tissue regeneration. In other embodiments, the first basestructure 100 and the second base structure 200 correspond to differentportions of a bone loss, and are configured for the regeneration of thetissues in the different portions of the bone loss. The differentportions of the bone loss have different properties, for example, onebone loss portion has a higher density than the other portion of thebone loss.

FIG. 2A schematically shows a biocompatible structure 90 according tocertain embodiments of the present disclosure. The biocompatiblestructure 90 can includes one or more base structures. In oneembodiment, the biocompatible structure 90 includes a first basestructure 100 and a second base structure 200. Each of the basestructures can be in any shape that conforms to a shape or part of ashape of an implant site. For example, each of the base structures canhave a cylindrical shape, a rectangular shape, or a spherical shape.

As shown in FIGS. 2A-2C, the biocompatible structure 90 includes thefirst base structure 100, the second base structure 200, and a coating300 surrounding the first base structure 100 and the second basestructure 200.

The first base structure 100 includes two or more first polymer layers102 stacked together. Only three first polymer layers 102-1, 102-2, and102-3 are shown in FIG. 2A. However, as shown in FIG. 2B, the number ofthe first polymer layers 102 can be m, where m is a positive integer. Incertain embodiments, the first base structure 100 includes the firstpolymer layer 102-1, the first spacer layer 106-1, the first polymerlayer 102-2, the first spacer layer 106-2, the first polymer layer102-3, the second spacer layer 106-3 . . . the first spacer layer 106-(m-1), the first polymer layer 102-m, and optionally the first spacerlayer 106-m stacked layer by layer. As will be described below, thefirst polymer layers 102 each have first tissue forming nanoparticles112 dispersed in a first polymer matrix 114. In certain embodiments, thesize of the first tissue forming nanoparticles 112 is about 0.1 nm to1000 nm. In certain embodiments, the size of the first tissue formingnanoparticles 112 is about 1 nm to 500 nm. In certain embodiments, thesize of the first tissue forming nanoparticles 112 is about 2-300 nm. Incertain embodiments, the size of the first tissue forming nanoparticles112 is about 50-150 nm. In certain embodiments, the first tissue formingnanoparticles 112 are hydroxypatite (HAP) nanoparticles. In certainembodiments, the thickness of the first polymer layers 102 is about0.001 mm-100 mm. In certain embodiments, the thickness of the firstpolymer layers 102 is about 0.01 mm-50 mm. In certain embodiments, thethickness of the first polymer layers 102 is about 0.1 mm-20 mm. Incertain embodiments, the thickness of the first polymer layers 102 isabout 1 mm-3 mm. In certain embodiments, the first polymer layers 102can be made as strips. In certain embodiments, the first polymer layers102 each can have a length of 0.005-50 cm, a width of 0.002-50 cm, and athickness of 0.001-50 mm. In certain embodiments, the first polymerlayers 102 each can have a length of 0.05-10 cm, a width of 0.02-5 cm,and a thickness of 0.01-5 mm. In certain embodiments, the first polymerlayers 102 each can have a length of 0.5-5 cm, a width of 0.2-3 cm, anda thickness of 0.1-3 mm. In certain embodiments, the first polymerlayers 102 each can have a length of about 1-3 cm, a width of about0.5-2 cm, and a thickness of about 0.5-2 mm. Further, first spacerparticles 116 are located in between any two of the first polymer layers102 and can function as a first spacer layer 106 between the firstpolymer layers 102. In certain embodiments, the first spacer particles116 each have a diameter of about 2-100 μm. In certain embodiments, thefirst spacer particles 116 each have a diameter of about 0.5-1000 μm. Incertain embodiments, the first spacer particles 116 each have a diameterof about 2-100 μm. In certain embodiments, the first spacer particles116 each have a diameter of about 10-50 μm. In certain embodiments, thefirst spacer particles 116 are partially embedded, or trapped, in thesurface portion of the first polymer layers 102. In certain embodiments,each first spacer layer 106 can have a thickness between approximately0.001 mm and approximately 50 mm. In certain embodiments, the thicknessof the first spacer layers 106 is about 0.001 mm-100 mm. In certainembodiments, the thickness of the first spacer layers 106 is about 0.01mm-50 mm. In certain embodiments, the thickness of the first spacerlayers 106 is about 0.1 mm-20 mm. In certain embodiments, the thicknessof the first spacer layers 106 is about 1 mm-3 mm. In certainembodiments, each first spacer layer 106 can have a thickness betweenapproximately 0.001 mm and approximately 50 mm, but are typically lessthan 3 mm. The layers can be stacked in vitro, in vivo, or in situ ontop of one another. In certain embodiments, the first spacer particles116 can be bone particles or composite particulates as described below.In certain embodiments, the first spacer particles 116 can be HAPparticles as described below. In certain embodiments, a portion of onefirst polymer layer 102 can contact a portion of an adjacent firstpolymer layer 102. In certain embodiments, those contacted portions cancross-link with each other. In certain embodiments, the base 100, iscovered or contains a surface film formed of a hydrophilic polymericstructure that has a high capacity for liquid absorption such thatimmediately upon insertion, the scaffold increases slightly in size andlocks itself in the bone defect.

The second base structure 200 includes two or more second polymer layers202 stacked together. Only three second polymer layers 202-1, 202-2, and202-3 are shown in FIG. 2A. However, as shown in FIG. 2B, the number ofthe second polymer layers 202 can be n, where n is a positive integer.The integers m and n can be the same value or different value, accordingto the size and thickness needed for the first base structure 100 andthe second base structure 200. In certain embodiments, the second basestructure 200 includes the second polymer layer 202-1, the second spacerlayer 206-1, the second polymer layer 202-2, the second spacer layer206-2, the second polymer layer 202-3, the second spacer layer 206-3 . .. the second spacer layer 206- (n-1), the second polymer layer 202-n,and optionally the second spacer layer 206-n stacked layer by layer onthe first base structure 100. In certain embodiments, the first basestructure and the second base structure is separated by a first spacerlayer 106 or a second spacer layer 206. In certain embodiments, thefirst base structure and the second base structure has a first polymerlayer 102-second spacer layer 206 interface. In certain embodiments, thefirst base structure and the second base structure has a first polymerlayer 102-second polymer layer 202 interface. In certain embodiments,the first base structure and the second base structure has a firstspacer layer 106-second polymer layer 202 interface. In certainembodiments, the first base structure and the second base structure hasa first spacer layer 106-second spacer layer 206 interface.

As will be described below, the second polymer layers 202 each havesecond tissue forming nanoparticles 212 dispersed in a second polymermatrix 214. In certain embodiments, the size of the second tissueforming nanoparticles 212 is about 0.1 nm to 1000 nm. In certainembodiments, the size of the second tissue forming nanoparticles 212 isabout 1 nm to 500 nm. In certain embodiments, the size of the secondtissue forming nanoparticles 212 is about 2-300 nm. In certainembodiments, the size of the second tissue forming nanoparticles 112 isabout 50-150 nm. The size of the second tissue forming nanoparticles 212can be the same as or different from the first tissue formingnanoparticles 112. In certain embodiments, the first base structure 100and the second base structure 200 are configured for regeneration ofdifferent bone portions, and the second tissue forming nanoparticles 212are hydroxyapatite (HAP) nanoparticles. In certain embodiments, thefirst base structure and the second base structure 200 are configuredfor regeneration of bone loss and muscle tissue loss of an implant siterespectively, and the second tissue forming nanoparticles 212 arepolymeric nanoparticles or nanofibers. In certain embodiment, the HAPnanoparticle is not suitable as the second tissue forming nanoparticle212 when the second base structure 200 is configured for theregeneration of muscle tissue. In certain embodiments, the secondpolymer layers 202 can be made as strips. In certain embodiments, thesecond polymer layers 202 each can have a length of 0.005-50 cm, a widthof 0.002-50 cm, and a thickness of 0.001-50 mm. In certain embodiments,the second polymer layers 202 each can have a length of 0.05-10 cm, awidth of 0.02-5 cm, and a thickness of 0.01-5 mm. In certainembodiments, the second polymer layers 202 each can have a length of0.5-5 cm, a width of 0.2-3 cm, and a thickness of 0.1-3 mm. In certainembodiments, the second polymer layers 202 each can have a length ofabout 1-3 cm, a width of about 0.5-2 cm, and a thickness of about 0.5-2mm.

Further, second spacer particles 216 are located in between any two ofthe second polymer layers 202 and can function as a second spacer layer206 between the second polymer layers 202. In certain embodiments, thesecond spacer particles 216 each have a diameter of about 0.002-100 μm.In certain embodiments, the second spacer particles 216 each have adiameter of about 0.002-1000 μm. In certain embodiments, the secondspacer particles 216 each have a diameter of about 0.002-100 μm. Incertain embodiments, the second spacer particles 216 each have adiameter of about 10-50 μm. In certain embodiment, the second spacerparticles 216 can be the same as or different from the first spacerparticles 116. In certain embodiments, the second spacer particles 216are partially embedded, or trapped, in the surface portion of the secondpolymer layers 202. In certain embodiment, the second spacer particles206 are polymeric nanoparticles or polymeric nanofibers. The secondpolymeric nanoparticles 216 or the second polymeric nanofibers 206 canbe deposited on the second polymer layer 202 by electrospray, air spray,or any other method that can deposit polymeric nanoparticles ornanofibers. In certain embodiments, each second spacer layer 206 canhave a thickness between approximately 0.001 mm and approximately 50 mm.In certain embodiments, the thickness of the second spacer layers 206 isabout 0.001 mm-100 mm. In certain embodiments, the thickness of thesecond spacer layers 206 is about 0.01 mm-50 mm. In certain embodiments,the thickness of the second spacer layers 206 is about 0.1 mm-20 mm. Incertain embodiments, the thickness of the second spacer layers 206 isabout 1 mm-3 mm. In certain embodiments, each second spacer layer 206can have a thickness between approximately 0.001 mm and approximately 50mm, but are typically less than 3 mm. In certain embodiment, the secondspacer layers 206 can have a thickness the same as or different from thethickness of the first spacer layers 106. The layers can be stacked invitro, in vivo, or in situ on top of one another. In certainembodiments, the second spacer particles 216 can be bone particles orcomposite particulates as described below. In certain embodiment, whenthe second base structure 200 is configured for muscle regeneration, thesecond spacer particles 216 are polymeric nanoparticles that are not HAPnanoparticles, or the second spacer particles 216 are polymericnanofibers. In certain embodiments, a portion of one second polymerlayer 202 can contact a portion of an adjacent second polymer layer 202.In certain embodiments, those contacted portions can cross-link witheach other.

In certain embodiments, the first base structure 100 and the second basestructure 200 have different properties. In certain embodiments, thefirst tissue forming nanoparticles 112 and the second tissue formingnanoparticles 212 are the same material, the first polymer matrix 114and the second polymer matrix 214 are the same material, and the firstspace particles 116 and the second space particles 216 are the samematerial. Alternatively, in certain embodiments, the first polymermatrix 114 and the second polymer matrix 214 are the same material, butthe first tissue forming nanoparticles 112 and the second tissue formingnanoparticles 212 are different material, and the first space particles116 and the second space particles 216 are different material.

In certain embodiments, both the first tissue forming nanoparticles 112and the second tissue forming nanoparticles are HAP nanoparticles, andthe weight percentages of HAP nanoparticles in the polymer film of thefirst base structure 100 and the second base structure 200 aredifferent. In one embodiment, the weight percentage of HAP nanoparticlesin the first polymer film 102 is greater than the weight percentage ofHAP nanoparticles in the second polymer film 202. In certainembodiments, the distances between the polymer layers of the first basestructure 100 and the second base structure 200 are different. In oneembodiment, the distance between the first polymer layers 102 in thefirst base structure 100 is less than the distance between the secondpolymer layers 202 in the second base structure 200. In certainembodiments, at least one of the size, shape, density, and porosity ofthe first spacer particles 116 in the first base structure 100 isdifferent from that of the second spacer particles 216 in the secondbase structure 200. In certain embodiments, the density of the firstspacer layer 106 is higher than the density of the second spacer layerin 206. In certain embodiment, the density of a layer is the weight (forexample, in grams) per volume (for example, in cubic millimeters).Alternatively, the density of a layer can be the number of particles(for example, number of nanoparticles) per volume (for example, in cubicmillimeters). In certain embodiments, the thickness of the first spacerlayer 106 in the first base structure 100 is different from thethickness of the second spacer layer 206 in the second base structure200. In certain embodiments, the thickness of the first spacer layer 106in the first base structure 100 is greater than the thickness of thesecond spacer layer 206 in the second base structure 200. In certainembodiments, the first base structure 100 and the second base structure200 of the biocompatible structure can have different degradation rates.In certain embodiments, the degradation rate of the first base structure100 is slower than the degradation rate of the second base structure200.

In certain embodiments, the first tissue forming nanoparticles 112 areHAP nanoparticles and the second tissue forming nanoparticles 212 arepolymeric nanoparticles or nanofibers, and the weight percentages of HAPnanoparticles in the polymer film of the first base structure 100 andthe weight percentage of polymeric nanoparticles or nanofibers in thesecond base structure 200 are different. In one embodiment, the weightpercentage of HAP nanoparticles in the first polymer film 102 is greaterthan the weight percentage of polymeric nanoparticles or nanofibers inthe second polymer film 202. In certain embodiments, the distancesbetween the polymer layers of the first base structure 100 and thesecond base structure 200 are different. In one embodiment, the distancebetween the first polymer layers 102 in the first base structure 100 isless than the distance between the second polymer layers 202 in thesecond base structure 200. In certain embodiments, at least one of thesize, shape, density, and porosity of the first spacer particles 116 inthe first base structure 100 is different from that of the second spacerparticles 216 in the second base structure 200. In certain embodiments,the density of the first spacer layer 106 is higher than the density ofthe second spacer layer in 206. In certain embodiment, the density of alayer is the weight per volume (for example, grams/cubic millimeters).Alternatively, the density of a layer can be the number of particles pervolume (for example, number of nanoparticles/cubic millimeters ormole/cubic millimeter). In certain embodiments, the thickness of thefirst spacer layer 106 in the first base structure 100 is different fromthe thickness of the second spacer layer 206 in the second basestructure 200. In certain embodiments, the thickness of the first spacerlayer 106 in the first base structure 100 is greater than the thicknessof the second spacer layer 206 in the second base structure 200. Incertain embodiments, the first base structure 100 and the second basestructure 200 of the biocompatible structure can have differentdegradation rates. In certain embodiments, the degradation rate of thefirst base structure 100 is slower than the degradation rate of thesecond base structure 200.

In certain embodiments, the biocompatible structure 90 includes apolymer coating 300 enclosing the stacked base structures 100 and 200.In certain embodiments, the surface of the coating 300 can have trappedthird spacer particles 316. In certain embodiments, the third spacerparticles 316 can form a layer and cover a substantial portion of theentire coating 300. The material of the third spacer particles 316 canbe the same as the material of the first spacer particle 106 or thesecond spacer particle 206. In certain embodiments, the third spacerparticles 316 each have a diameter of about 0.5-1000 μm. In certainembodiments, the third spacer particles 316 each have a diameter ofabout 2-100 μm. In certain embodiments, the third spacer particles 316each have a diameter of about 10-50 μm. In certain embodiment, the thirdspacer particles 316 can be the same as or different from the firstspacer particles 116 or the second spacer particles 216.

As discussed above, the first tissue forming nanoparticles 112 dispersedin the first polymer layer 102 or the second tissue formingnanoparticles 212 dispersed in the second polymer layer 202 are HAPnanoparticles and can have a dimensional range between 1-100 nanometer(nm). Hydroxylapatite, also called hydroxyapatite (HA or HAP), is anaturally occurring mineral form of calcium apatite with the formulaCa₅(PO₄)₃(OH), but is usually written Ca₁₀(PO₄)₆(OH)₂to denote that thecrystal unit cell comprises two entities. Hydroxylapatite is thehydroxyl endmember of the complex apatite group. The OH⁻ ion can bereplaced by fluoride, chloride or carbonate, producing fluorapatite orchlorapatite. It crystallizes in the hexagonal crystal system. Purehydroxylapatite powder is white. Naturally occurring apatites can,however, also have brown, yellow, or green colorations, comparable tothe discolorations of dental fluorosis. Up to 50% of bone by weight is amodified form of hydroxylapatite (known as bone mineral). In certainembodiments, the HAP nanoparticles dispersed in the polymer layer can becomposed of pure HAP, having significant crystallinity and very gooddispensability due to the presence of oxygen groups on the surface.

The presence of first HAP nanoparticles 112 in the first polymer film114, among other things, contributes to the pore size and the strengthof the first polymer film 114. In addition, the concentration of firstHAP nanoparticles 112 is also related to the degradation rate of thefirst polymer film 114 when the first polymer film 114 is used asimplant material. The presence of second HAP nanoparticles 212 in thesecond polymer film 214, among other things, contributes to the poresize and the strength of the second polymer film 214. In addition, theconcentration of second HAP nanoparticles 212 is also related to thedegradation rate of the second polymer film 214 when the second polymerfilm is used as implant material.

In certain embodiments, the first HAP nanoparticles 112 can enhancebone/mineralization in bone cells. The first HAP nanoparticles 112,together with other nanomaterials, have the ability to increase theosteogenesis and mineralization in bone cells. In certain embodiments,the second HAP nanoparticles 212, together with other nanomaterials,have the ability to increase the growth of muscle cells.

In other embodiments, the first tissue forming nanoparticles 112dispersed in the first polymer layer 102 are HAP nanoparticles and thesecond tissue forming nanoparticles 212 dispersed in the second polymerlayer 202 are polymeric nanoparticles or nanofibers. The HAPnanoparticles 112 and the nanofibers 212 can have a dimensional rangebetween 1-100 nanometer (nm).

The presence of first HAP nanoparticles 112 in the first polymer film114, among other things, contributes to the pore size and the strengthof the first polymer film 114. In addition, the concentration of firstHAP nanoparticles 112 is also related to the degradation rate of thefirst polymer film 114 when the first polymer film 114 is used asimplant material. The presence of nanofibers of polymeric nanoparticles212 in the second polymer film 214, among other things, contributes tothe pore size and the strength of the second polymer film 214. Inaddition, the concentration of the nanofibers of polymeric nanoparticles212 is also related to the degradation rate of the second polymer film214 when the second polymer film is used as implant material.

In certain embodiments, the first HAP nanoparticles 112 can enhancebone/mineralization in bone cells. The first HAP nanoparticles 112,together with other nanomaterials, have the ability to increase theosteogenesis and mineralization in bone cells. In certain embodiments,the nanofibers or polymeric nanoparticles 212, together with othernanomaterials, have the ability to increase the growth of muscle cells.

In certain embodiment, the first spacer particles 116 between the firstpolymer layers 102 or the second spacer particles 216 between the secondpolymer layers 202 of the present disclosure are bone particles,polymeric nanoparticles, or polymeric nanofibers. In certain embodiment,the bone particles can be autografts, allografts, xenografts (usuallybovine) or alloplastic bone grafts (synthetic, such as tricalciumphosphate). In certain embodiment, the first and second bone particles116 and 216 are treated with bone mineral products, or compositeparticles. Bones from slaughtered animals are an inexpensive rawmaterial available in large quantities to produce bone mineral. Bonestypically contain 50 to 60% of very fine crystallites of a form ofmodified hydroxylapatite, which is bonded by collagenic tissue andcontains significant qualities of proteinaceous and other matter as wellas associated fat and muscle tissues. Such a modified hydroxylapatite,in a pure state and has its essential crystal structure, represents ahighly biocompatible remodeling bone implant material. In certainembodiments, the first and second bone particles 116 and 216 includehydroxyapatite like crystallites with a particular degree ofcrystallinity, habit, and size (irregular platelike morphology, 5-10 nmin thickness 10-50 nm in length). The specific surface chemistry of thefirst and second bone particles 116 and 216 results from the calcium tophosphate ratio (37.5-38.0% calcium and 15.5-19.0% phosphorus). Theinorganic phase of the first and second bone particles 116 and 216contains porosity including ultrastructural interstices (10-100 nm)between the crystallites occurring naturally and produced by removal ofthe organic phase, and microscopic spaces (1-20 μm) including osteocytelacunae, canaliculi, vascular channels, volkman's canals, and the canalsof haversian systems (100-500 nm). The specific surface area, which is ameasure of porosity is in the range 50 to 100 m²/gram as determined bymercury porosimetry. The crystallinity of the first and second boneparticles 116 and 216 can be characterized by X-ray diffraction and theporosity and crystallite morphology and size by electron microscopy.

In certain embodiment, the first and second bone particles 116 and 216of the present disclosure are demineralized bone particles purchasedfrom Geistlich BioOss, INC. The first and second bone particles 116 and216 can be of bovine origin and treated such that only the inorganicstructure is left, while the organic materials are removed. The firstand second bone particles 116 and 216 are composed of powder particleswith a diameter of 0.01-100 micrometer (μm).

In certain embodiments, the first and second spacer particles 116 and216 can be large particles of HAP that, e.g., are produced in the lab,or composite particles (polymer and inorganic particles).

In certain embodiments, the spacers 216 can be polymer particles,polymer nanoparticles, or nanofibers with a diameter ranging from 2 nmto 100 microns. The length of the nanofibers can vary from 2 nm to a fewcentimeters and can be produced from the same polymer used for layer 202or from a different polymer.

In certain embodiments, the first base structure 100 can include firstbioactive materials 126. In certain embodiments, the first bioactivematerials 126 can be sprayed on the surface of the first base structure100, and/or incorporated in the first polymer structures 102 to promotebone growth.

In certain embodiments, the second base structure 200 can include secondbioactive materials 226. In certain embodiments, the second bioactivematerials 226 can be sprayed on the surface of the second base structure200, and/or incorporated in the second polymer structures 202 to promotemuscle growth.

The first and second bioactive materials 126 and 226 can beproteins/peptides, HA, drugs, growth factors, antibiotics (such astetracycline, tobramycin, or others), and bone morphogenic proteins.Preferred first and second bioactive agents 126 and 226 are those thatenhance tissue regeneration and/or tissue adhesion. Illustrativeexamples include growth factors, antibiotics, immuno-stimulators, andimmuno-suppressants. In one embodiment, one of the first and secondbioactive agents 126 and 226 may be a bone morphogenic protein such asbone morphogenetic proteins (BMP). In another embodiment, one of thesecond and the first bioactive agents 226 and 126 may be a growth factorsuch as fibroblast growth factors (FGF) or an agent which promotes thegeneration of connective tissue. In certain embodiments, the firstbioactive agent 126 promotes regeneration of bone tissue and the secondbioactive agent 226 promotes regeneration of muscle tissue.

In certain embodiments, tissue can also be grown in vivo by implantingthe biocompatible structure 90 and stem cells or other types of suitablecells (liver cells for the growth of liver tissue; myocardial cells,muscle cells for replacing/restoring damaged heart tissue; epithelialcells, connective tissue cells for skin grafts; osteblasts for bonegeneration) to an implant site. Alternatively, tissue can be grown invitro on the biocompatible structure 90 and then implanted (for example,for growth of connective tissue/coronary vessels for arterial grafts).

Suitable living cells can be placed in the biocompatible structure 90before implantation or implanted together with the biocompatiblestructure 90 into a body. The living cells include epithelial cells(e.g., keratinocytes, adipocytes, hepatocytes), neurons, glial cells,astrocytes, podocytes, mammary epithelial cells, islet cells,endothelial cells (e.g., aortic, capillary and vein endothelial cells),and mesenchymal cells (e.g., dermal fibroblasts, mesothelial cells,osteoblasts), smooth muscle cells, striated muscle cells, ligamentfibroblasts, tendon fibroblasts, chondrocytes, fibroblasts, and any of avariety of stem cells. Also suitable for use in the biocompatiblestructure 90 having one or more base structures are genetically modifiedcells, immunologically masked cells, and the like. Appropriateextracellular matrix proteins (ECM) may be added to the biocompatiblestructure to further promote cell ingrowth, tissue development, and celldifferentiation within the scaffold. ECM proteins can include one ormore of fibronectin, laminin, vitronectin, tenascin, entactin,thrombospondin, elastin, gelatin, collagen, fibrillin, merosin,anchorin, chondronectin, link protein, bone sialoprotein, osteocalcin,osteopontin, epinectin, hyaluronectin, undulin, epiligrin, and kalinin.

Additional first and second bioactive agents 126 and 226 incorporated inthe first base structure 100 and the second base structure 200, amongother things, includes biologically active macromolecules helpful forcell growth, morphogenesis, differentiation, and tissue building,include growth factors, proteoglycans, glycosaminoglycans andpolysaccharides. These compounds are believed to contain biological,physiological, and structural information for development orregeneration of tissue structure and function.

In certain embodiments, the biocompatible structure 90 having one ormore base structures can be plasma-treated/activated/electro-sprayed tofunctionalize the surface of the biocompatible structure 10. Surfacetreatment can improve the hydrophilicity of the biocompatible structure90 and promote the colonization of cells and the adhesion of boneparticles to the surface and pores of the biocompatible structure 10.The surface can also be functionalized by electron or ion bombardment,laser irradiation and/or by any other physical or chemical surfacereaction that affects the bonds near the surface. These processes canalso help in sterilization of the implant. Plasma treatment breaks thesurface bonds of the polymer. The plasma treatment may be a nitrogen oroxygen plasma treatment. In one example, after oxygen plasma treatment,oxygen atoms “attach” to the surface, changing the surface energy of thesurface such that the surface becomes more hydrophilic and has oxygenand nitrogen rich functional groups.

The biocompatible structure 90 having the one or more base structures ofthe present disclosure is highly porous (for example, high surface area,the presence of voids, cavities, etc.), biocompatible, and allows forvascular ingrowth for bone/tissue regeneration. The surface typicallydoes not inhibit any biological entity from interacting and to behydrophilic or potentially become hydrophilic under different conditionsor processes. Suitable materials for building structures for tissue/boneengineering and regeneration are certain polymers, ceramics,carbon-based materials and metals and metal composites. In certainembodiments, the first polymer layers 102 of the first base structure100 or the second polymer layers 202 of the second base structure 200 ofthe present disclosure are formed from polyurethane. In certainembodiments, the biocompatible structure 90 has a layered structurecomposed of a polymeric material that may contain other substances, suchas bioactive substances or substances promoting the generation of tissuegrowth. Those substances can be formed inside the first polymer layer102 or on the surface of the polymer layer 102, and/or inside the secondpolymer layer 202 or on the surface of the second polymer layer 202.Some of the bioresorbable polymers may or may not require enzymes inorder to degrade. The layered, porous design gives this structure a veryhigh surface area for neovascularization and the growth of cellsnecessary for tissue regeneration. In addition, stem cells, osteoblasts,and other types of suitable cells can be incorporated into the system toaid in tissue generation. The biocompatible structure 90 can assumedifferent shapes and dimensions as may be required for a particularapplication. The biocompatible structure 90 can be properly positionedin the surgical site directly or with medical pins, screws, or otherdevices.

The biocompatible structure 90 having one or more base structures isconfigured such that the degradation rate or the resorption rate of thebiocompatible structure 90 is substantially matching a rate of tissuegeneration in the biocompatible structure 10. The controllabledegradation rate of the biocompatible structure 90 can also providecontrollable release of the bioactive substance or cells formed in thebiocompatible structure 10. The polymer may have a different degradationrate than that of the biocompatible structure 10, but it contributessignificantly to the degradation rate of the biocompatible structure 10.Accordingly, a polymer with suitable degradation property is chosen toproduce the biocompatible structure 90 of the present disclosure. Incertain embodiments, the first base structure 100 portion and the secondbase structure 200 portion of the biocompatible structure 200 havedifferent degradation rates that corresponding respectively to thetissue type of the different part of the implant site.

The polymer layers 102 and 202 can be degraded by several mechanisms.The most common mechanism is diffusion. Further, the bioactivesubstances (agent) of the biocompatible structure can diffuse in variousmanners. The bioactive agent (drug) can have a core surrounded by aninert diffusion barrier, which can be membranes, capsules,microcapsules, liposomes, and hollow fibers. Alternatively, the activeagent can be dispersed or dissolved in an inert polymer. Drug diffusionthrough the polymer matrix is the rate-limiting step, and release ratesare determined by the choice of polymer and its consequent effect on thediffusion and partition coefficient of the drug to be released. Byadjusting the diffusion method of the bioactive agent or cells, andcomponents of the biocompatible structure component, suitable rate ofbioactive agent or cells is achieved.

In certain embodiments, after implantation the biocompatible structure90 can be eventually absorbed by the body, for example, by conversion ofa material that is insoluble in water into one that iswater/liquid-soluble, and thus need not be removed surgically.

In certain embodiments, the polymer layers 102 or 202 in thebiocompatible structure 90 are biocompatible, processable, sterilizable,and capable of controlled stability or degradation in response tobiological conditions. The reasons for designing a biocompatiblestructure10 that degrades over time often go beyond the obvious desireto eliminate the need for retrieval. For example, the very strength of arigid metallic implant used in bone fixation can lead to problems with“stress shielding,” whereas a bioresorbable implant can increaseultimate bone strength by slowly transferring load to the bone as itheals. For drug delivery, the specific properties of various degradablesystems can be precisely tailored to achieve optimal release kinetics ofthe drug or active agent.

An ideal biodegradable polymer layer 102 or 202 for medical applicationstypically has adequate mechanical properties to match the application(strong enough but not too strong), does not induce inflammation orother toxic response, may be fully metabolized once it degrades, and issterilizable and easily processed into a final end product with anacceptable shelf life. In general, polymer degradation is accelerated bygreater hydrophilicity in the backbone or end groups, greater reactivityamong hydrolytic groups in the backbone, less crystallinity, greaterporosity, and smaller finished device size.

A wide range of synthetic biodegradable polymers can be used to form thepolymer matrix 102 or 202 of the present disclosure, includingpolylactide (PLA), polyglycolide (PGA), poly(lactide-co-glycolide)(PLGA), poly(e-caprolactone), polydioxanone, polyanhydride, trimethylenecarbonate, poly(β-hydroxybutyrate), poly(g-ethyl glutamate), poly(DTHiminocarbonate), poly(bisphenol A iminocarbonate), poly(ortho ester),polycyanoacrylate, and polyphosphazene. There are also a number ofbiodegradable polymers derived from natural sources such as modifiedpolysaccharides (cellulose, chitin, dextran) or modified proteins(fibrin, casein) that can be used to form the polymer matrix of thepresent disclosure.

Other materials can be tyrosine-derived polycarbonate poly(DTE-co-DTcarbonate), in which the pendant group via the tyrosine-an amino acid-iseither an ethyl ester (DTE) or free carboxylate (DT). Through alterationof the ratio of DTE to DT, the material's hydrophobic/hydrophilicbalance and rate of in vivo degradation can be manipulated. It was shownthat, as DT content increases, pore size decreases, the polymers becomemore hydrophilic and anionic, and cells attach more readily. Thesematerials are subject to both hydrolysis (via ester bonds) and oxidation(via ether bonds). Degradation rate is influenced by PEO molecularweight and content, and the copolymer with the highest water uptakedegrades most rapidly.

These polymeric materials 102 and/or 202 can also be developed in such away that they are stable in the biological environment, and degrade onlyunder specific enzymatic conditions (plasmin, etc.). These materials canalso include partially expressed fragments of human or animal fibrinsuch that the system degrades only in contact with plasmin.

The polymer 114 and/or 214 is preferably in solution mixed with asuitable solvent, and other substances can be added to the solution, forexample, collagen, drugs, proteins, pep tides, hydroxyapetite crystals(HA), and antibiotics, depending on the type of tissue to be grown. Thesolution can be sonicated to promote mixing of the constituents.

By chosen a suitable polymer 114 and/or 214, the biocompatible structure90 can achieve controllable supply of therapeutic, analgesic and/orantibacterial substances, growth factors, proteins, peptides, drugs,tissue subcomponents including but not limited to bone particles andhydroxyappetite, which promote growth, prevent infections and the like.

In certain embodiment, the biocompatible structure includes one or morebase structures. The one or more base structures can have differentproperties. For example, for the biocompatible structure 90 having thefirst base structure 100 and the second base structure 200, the basestructures 100 and 200 can have different properties as follows.

In certain embodiments, the weight percentage of the first tissueforming nanoparticles 112 in the first polymer film/layer 102 is definedas the total weight (e.g., grams) of the first tissue formingnanoparticles 112 divided by the total of the weight of the first tissueforming nanoparticles 112 (grams) and the weight of the solid firstpolymers 114 (grams) used for the preparation of the first polymer film102. For example, a total of A grams of first nanoparticles 112 and atotal of B grams of first polymers 114 are used to manufacture a firstpolymer film 102. The weight percentage of the first tissue formingnanoparticles 112 in the first polymer film 102 is calculated asA/(A+B). In certain embodiments, the weight percentage of the firsttissue forming nanoparticles 112 in the polymer layer 102 is about0.05-95%. In certain embodiments, the weight percentage of the firsttissue forming nanoparticles 112 in the polymer layer 102 is about5-60%. In certain embodiments, the weight percentage of the first tissueforming nanoparticles 112 in the polymer layer 102 is about 10-30%. Incertain embodiments, the weight percentage of the first tissue formingnanoparticles 112 in the polymer layer 102 is about 15-25%. In certainembodiments, the weight percentage of the tissue forming nanoparticles112 in the polymer layer 102 is about 20%. In certain embodiment, thesecond polymer layer 202 can have similar features or different featuresas the first polymer layer 102. In certain embodiment, the weightpercentage of the second tissue forming nanoparticles 212 in the polymerlayer 202 is lower than that in the first polymer layer 102. In certainembodiment, the polymer layer 202 may not contain tissue formingnanoparticles 212. In certain embodiment, the weight percentage oftissue forming nanoparticles 212 in the polymer layer 202 is 0.1-50%lower than that in the first polymer layer 102. In certain embodiment,the weight percentage of tissue forming nanoparticles 212 in the polymerlayer 202 is 1-5% lower than that in the first polymer layer 102. Incertain embodiment, the weight percentage of tissue formingnanoparticles 212 in the polymer layer 202 is 2% lower than that in thefirst polymer layer 102 In certain embodiments, the first polymer matrix114 of the first polymer layer 102 can be polyurethane. The first tissueforming nanoparticles 112 dispersed in the first polymer matrix 114 canbe HAP nanoparticles. In certain embodiments, the second polymer matrix214 of the second polymer layer 202 can be polyurethane. The secondtissue forming nanoparticles 212 dispersed in the second polymer matrix214 can be HAP nanoparticles, such that the first base structure 100 andthe second base structure 200 are configured to regenerate differentportions of a bone loss. In other embodiments, the second tissue formingnanoparticles 212 dispersed in the second polymer matrix 214 can bepolymeric nanoparticle or nanofibers, such that the first base structure100 and the second base structure 200 are configured to regenerate abone loss and a muscle loss of an implant site respectively.

In certain embodiments, the first tissue forming nanoparticles 112 andthe second tissue forming nanoparticles 212 are HAP nanoparticles, andthe first polymer 114 and the second polymer 214 are the same polymer.The weight percentage of HAP nanoparticles in the polymer film isdifferent in the first base structure 100 and the second base structure200. In one embodiment, a first weight percentage of HAP nanoparticle inthe first polymer layer 102 of the first base structure 100 is 10-30%,and a second weight percentage of HAP nanoparticle in the second polymerlayer 202 of the second base structure 200 is 8-28%. In one embodiment,the first weight percentage is 15-25%, and the second weight percentageis 13-23%. In one embodiment, the first weight percentage is 18-22%, andthe second weight percentage is 16-20%. In one embodiment, the firstweight percentage is 20%, and the second weight percentage is 18%. Incertain embodiments, the thickness of the first polymer layer 102 in thefirst base structure 100 is different from the thickness of the secondpolymer layer 202 in the second base structure 200.

In certain embodiments, the first tissue forming nanoparticles 112 areHAP nanoparticles, the second tissue forming nanoparticles 212 arenanofibers or polymeric nanoparticles, and the first polymer 114 and thesecond polymer 214 are the same polymer. The weight percentage of HAPnanoparticles in the first polymer film 102 is different from thenanofiber or polymeric nanoparticles in the second polymer film 202. Inone embodiment, a first weight percentage of HAP nanoparticle in thefirst polymer layer 102 of the first base structure 100 is 10-30%, and asecond weight percentage of nanofiber or polymeric nanoparticles in thesecond polymer layer 202 of the second base structure 200 is 8-28%. Inone embodiment, the first weight percentage is 15-25%, and the secondweight percentage is 13-23%. In one embodiment, the first weightpercentage is 18-22%, and the second weight percentage is 16-20%. In oneembodiment, the first weight percentage is 20%, and the second weightpercentage is 18%. In certain embodiments, the thickness of the firstpolymer layer 102 in the first base structure 100 is different from thethickness of the second polymer layer 202 in the second base structure200.

In certain embodiments, the size and shape of the first polymer layer102 in the first base structure 100 are different from the size andshape of the second polymer layer 202 in the second base structure 200.

In certain embodiments, the thickness of the first polymer layer 102 andthe second polymer layer 202 is about 0.001 mm-50 mm. In certainembodiments, the thickness of the first polymer layer 102 is differentfrom the thickness of the second polymer layer 202. In certainembodiments, the thickness of the first polymer layer 102 is smallerthan the thickness of the second polymer layer 202. In certainembodiments, the thickness of the first polymer layer 102 is about 0.1mm-20 mm, and the thickness of the second polymer layer 202 is about 0.2mm-30 mm. In certain embodiments, the thickness of the first polymerlayer 102 is about 2 mm-5 mm, and the thickness of the second polymerlayer 202 is about 3 mm-10 mm. In certain embodiments, the thickness ofthe first polymer layer 102 is about 3 mm, and the thickness of thesecond polymer layer 202 is about 5 mm.

In certain embodiments, the distances between the polymer layers in thefirst base structure 100 and the second base structure 200 aredifferent. In certain embodiments, the distance between the firstpolymer layers 102 is greater than the distance between the secondpolymer layers 202. In certain embodiments, the distance between thefirst polymer layers 102 is about 0.002 mm-50 mm, and the distancebetween the second polymer layers 202 is about 0.001-40 mm. In certainembodiments, the distance between the first polymer layers 102 is about0.02 mm-10 mm, and the thickness of the second spacer layer 206 is about0.01 mm-8 mm. In certain embodiments, the distance between the firstpolymer layers 102 is about 0.2 mm-8 mm, and the distance between thesecond polymer layers 202 is about 0.1 mm-6 mm. In certain embodiments,the distance between the first polymer layers 102 about 1 mm-5 mm, andthe distance between the second polymer layers 202 is about 0.5 mm-3 mm.In certain embodiments, the distance between the first polymer layers102 is about 2 mm, and the distance between the second polymer layers202 is about 1 mm.

In certain embodiments, the first spacer particles 116 in the first basestructure 100 are different from the second spacer particle 216 in thesecond base structure 200. In certain embodiments, the size, shape,density, and porosity of the first spacer particles 116 are differentfrom the size, shape, density, and porosity of the second spacerparticles 216. In certain embodiments, the density of the first spacerlayer 106 is higher than the density of the second spacer layer in 206.In certain embodiments, the porosity of the first spacer particles 116is less than the porosity of the second spacer particles 216. In certainembodiments, the porosity of the first spacer particles 116 is about50-90 m²/gram, and the porosity of the second spacer particles 216 isabout 60-100 m²/gram. In certain embodiments, the porosity of the firstspacer particles 116 is about 60-80 m²/gram, and the porosity of thesecond spacer particles 216 is about 70-90 m²/gram. In certainembodiments, the porosity of the first spacer particles 116 is about 70m²/gram, and the porosity of the second spacer particles 216 is about 80m²/gram. In certain embodiment, the first spacer particles 216 are boneparticles or bone nanoparticles, and the second spacer particles 226 arepolymeric nanoparticles or polymer nanofibers.

In certain embodiments, the thickness of the first spacer layer 106 inthe first base structure 100 is different from the thickness of thesecond spacer layer 206 in the second base structure 200. In certainembodiment, the thickness of the first spacer layer 106 is greater thanthe thickness of the second spacer layer 206. In certain embodiments,the thickness of the first spacer layer 106 is about 0.002 mm-50 mm, andthe thickness of the second spacer layer 206 is about 0.001 mm-40 mm. Incertain embodiments, the thickness of the first spacer layer is about0.02 mm-10 mm, and the thickness of the second spacer layer 206 is about0.01 mm-8 mm. In certain embodiments, the thickness of the first spacerlayer 106 is about 0.2 mm-8 mm, and the thickness of the second spacerlayer 206 is about 0.1 mm-6 mm. In certain embodiments, the thickness ofthe first spacer layer 106 is about 1 mm-5 mm, and the thickness of thesecond spacer layer 206 is about 0.5 mm-3 mm. In certain embodiments,the thickness of the first spacer layer 106 is about 2 mm, and thethickness of the second spacer layer 206 is about 1 mm.

In certain embodiments, the density of the first spacer layer 106 in thefirst base structure 100 is different from the density of the secondspacer layer 206 in the second base structure 200. In one embodiment,the density of the first spacer layer 106 is higher than the density ofthe second spacer layer in 206.

In certain embodiments, the first base structure 100 and the second basestructure 200 of the biocompatible structure 90 can have differentdegradation rates. In one embodiment, the degradation rate of the firstbase structure 100 is slower than the degradation rate of the secondbase structure 200.

When placed in an implant site, new tissue of a patient can grow acrossthe pores on the surface of the biocompatible structure, and inside thehollow interior of the biocompatible structure.

In certain embodiments, each of the first base structure 100 and thesecond base structure 200 of a biocompatible structure 90 can be seededwith the corresponding types of cells (or stem cells) for each tissue.For example, bone forming cells can be seeded to the first basestructure 100, and muscle cells can be seeded to the second basestructure 200.

In certain embodiments, each of the base structures in the biocompatiblestructure 90 can be decorated with antibiotics and or with correspondinggrowth factors.

In certain embodiments, each of the base structures can be doped withvarious nanomaterials both in the bulk as well as on the surface.

In certain embodiments, when placed in the implant site 50, due to itsmorphological characteristics, the biocompatible structure 90 absorbsliquid from the implant site 50 quickly, and expands about 2-5% involume, such that the biocompatible structure 90 locks itself into theimplant site 50 and stays well attached. In certain embodiments,according to the components of the biocompatible structure 90 having thefirst base structure 100 and the second base structure 200, thecondition of the patient, and the implant site 50, the biocompatiblestructure 90 expands about 1-50% in volume after being placed in theimplant site 50. In one embodiment, the biocompatible structure 90expands up to about 10-15% in volume after being placed in the implantsite 50. In one embodiment, the biocompatible structure 90 expands about2-5% in volume after being placed in the implant site 50. In oneembodiment, the biocompatible structure 90 expands about 4% in volumeafter being placed in the implant site 50. In certain embodiments, thefirst base structure 100 portion and the second base structure 200portion of the biocompatible structure 90 can have different expansionrate. For example, each of the first base structure 100 and the secondbase structure 200 of the biocompatible structure 90 has an expansionrate consistent with the requirement of their corresponding tissueportion of the implant site 50. In certain embodiments, according to thecomponents of the biocompatible structure 90 having the first basestructure 100 and the second base structure 200, the condition of thepatient, and the implant site 50, the first base structure 100 expandsabout 0-8% in volume after being placed in the bone area 500 of theimplant site 50, and the second base structure 200 expands about 1-10%in volume after being placed in the muscle area 600 of the implant site50. In certain embodiments, the expansion of the first base structure100 portion is lower than the expansion of the second base structure 200portion. In one embodiment, the first base structure 100 expands about1-5% in volume after being placed in the bone area 500, and the secondbase structure 200 expands about 2-6% in volume after being placed inthe muscle area 600. In one embodiment, the first base structure 100expands about 3% in volume after being placed in the bone area 500, andthe second base structure 200 expands about 4% in volume after beingplaced in the muscle area 600.

In certain embodiments, according to the components of the biocompatiblestructure 90 having the first base structure 100 and the second basestructure 200, the condition of the patient, and the condition of theimplant site 50, the expansion may occur at the first 30 days of theimplantation process. In one embodiment, the expansion occurs in thefirst 5 days of the implantation. In one embodiment, the expansionoccurs in the first 24 hours of the implantation. In one embodiment, theexpansion occurs in the first 12 hours of the implantation. In oneembodiment, the expansion occurs in the first 6 hours of theimplantation.

In one embodiment, the implant stabilized in the first 10 days. That is,the implant does not have substantially expansion after the first 10days. In one embodiment, the implant stabilized in the first 5 days. Inone embodiment, the implant stabilized in the first 24 hours. In oneembodiment, the implant stabilized in the first 12 hours. In oneembodiment, the implant stabilized in the first 6 hours.

In certain embodiments, the occurrence time of the expansion and thelasting period of the expansion for the first base structure 100 aredifferent from those of the second base structure 200.

FIG. 3A illustrates a biocompatible structure 30 having one basestructure according to certain embodiments of the present disclosure.

FIG. 3B schematically shows a Scanning Electron Microscopy image of thebiocompatible structure 30 having one base structure at a low resolutionaccording to certain embodiments of the present disclosure. Thebiocompatible structure 30 has bone particles 316 over porous polymermembrane matrix and a hollow interior to promote cellular growth andblood flow. In FIG. 3B, bioactive materials 326 are shown on the surfaceof the biocompatible structure 30. In certain embodiments, the bioactivematerials 326 can be sprayed on the surface of the biocompatiblestructure 30, and/or incorporated in the polymer layer to promote bonegrowth.

FIGS. 3C-3E schematically shows Scanning Electron Microscopy images ofthe biocompatible structure 30 having one base structure at highresolutions according to certain embodiments of the present disclosure.As shown in FIGS. 3C-3E, the surface of the biocompatible structure 30made from polyurethane polymer and hydroxyapatite nanoparticles can bevery rough and can have one or more polymeric pores 304. The polymericpores 304 typically are large in size. The size of the polymeric pores304 can be from about 0.001 μm up to about 10 mm. The nanostructuralhydroxyapatatite 308 at the surface of the biocompatible structure 30can have a size of about 1 nm to about 500 nm, and the majority of thenanostructural hydroxyapatite 308 can have a size of about 2 nm to about300 nm. Inside the biocompatible structure 30 is semi-empty due to thespacing between the layers offered by the bone particles. The pore sizeshould vary both in the range of nanometer (nm) and the range ofmicrometer (μm).

In certain embodiments, the biocompatible structure 90 useful for boneand tissue regeneration includes one or more base structures. Thebiocompatible structure 90 having two base structures 100 and 200 can beproduced by the following procedures.

As shown in FIG. 4A, in operation 402, a first polymer 114 is dissolvedin a first solvent to form a first solution.

In certain embodiments, the first polymer 114 can be a syntheticbiodegradable polymer, a biodegradable polymer derived from naturalsource, or their mixture. In certain embodiment, suitable syntheticbiodegradable polymer may include polyurethane, polylactide (PLA),polyglycolide (PGA), poly(lactide-co-glycolide) (PLGA),poly(e-caprolactone), polydioxanone, polyanhydride, trimethylenecarbonate, poly((β-hydroxybutyrate), poly(g-ethyl glutamate), poly(DTHiminocarbonate), poly(bisphenol A iminocarbonate), poly(ortho ester),polycyanoacrylate, polyphosphazene, or their mixture. In certainembodiments, the biodegradable polymer derived from natural source mayinclude modified polysaccharides (cellulose, chitin, dextran), modifiedproteins (fibrin, casein), or their mixture.

In certain embodiment, the first polymer 114 is ester-type hydrophilicpolyurethane with a linear expansion of 50-65%. The water uptake of thefirst polymer 114 varies with its composition, anywhere from 30-90%. Thefirst polymer 114 is thermoplastic. Alternatively, a thermosetting firstpolymer 114 may work equally well. In certain embodiment, the firstpolymer 114 may be mixed with other polymers to control its degradationrate. In certain embodiment, the polymer is a powder with particleshaving a diameter of about 0.02-50 mm.

The first solvent can be methanol or ethanol or any solvent of thepolymer used. In certain embodiment, other organic or inorganic solvent(polar aprotic and protic) may also be used. In certain embodiments, thesolvent is at least one of acetone, methyl ethyl ketone, nitromethane,n-propanol, n-butanol, isopropanol, propylene carbonate, dymethilsulfoxide, acetonitrile, dimethylformamide, ethyl acetate, andtetrahydrofuran, dichloromethane.

The first polymer 114 is evenly distributed in the first solution. Incertain embodiment, low power heating can be used to help thedissolvation of the polymer in the solvent. In certain embodiments,stirring is used to accelerate the uniform distribution of the polymerin the first solution. In certain embodiment, after completedissolvation of the solid polymer in the solvent, the first solution hasa low viscosity.

In operation 406, the first tissue forming nanoparticles 112 are addedto the first solution to form a second solution.

In certain embodiments, the first tissue forming material 112 mayinclude nanoparticles of hydroxyapatite (HAP), tricalcium phosphates,mixed calcium phosphates and calcium carbonate, bone particles ofzenograft, allografts, autografts, alloplastic grafts, or a mixturethereof.

In certain embodiment, the HAP nanoparticles 112 have a dimensionalrange between 1-100 nm. The HAP nanoparticles 112 can be composed ofpure HAP, having significant crystallinity, and having very gooddispensability due to the presence of oxygen groups on the surface.

The first polymer 114 and the first tissue forming material 112 areevenly distributed in the second solution. In certain embodiments,sonication is used to accelerate the homogenization of the first polymer114 and the first tissue forming material 112 in the second solution.

The weight percentage of the first polymer 114 to the first tissueforming material 112 in the second solution is about 20:1 to 2:1. Theratio is related with the characteristics of the produced first basestructure 100. The characteristics of the first base structure 100include resistance to load and stress, porosity, degradation rate, etc.In certain embodiments, the ratio of the polymer first 114 to the firsttissue forming material 112 can be adjusted to meet requirement of thecondition of a patient, including the bone or muscle implant position,size, and metabolic rate of the patient.

In certain embodiment, the first polymer 114 is polyurethane and thefirst tissue forming material 112 is HAP nanopowder containing HAPnanoparticles. The weight ratio of the added dry HAP nanopowder to thedry mass of the added polymer varies according to the purpose of use.

In certain embodiment, as described below in connection with FIGS. 8-9,if the first weight ratio of the dry HAP nanopowders to the dry mass ofpolyurethane is below 25% (i.e., the weight percentage of dry HAPnanopowder in the total weight of dry HAP nanopower and dry mass ofpolymer is about 20%), the produced first polymer film 102 as describedbelow is strong and hard. If the first weight percentage of the dry HAPnanopowders to the polyurethane is above 40%, the produced the polymerfilm as described below is weak and breaks easily. In certainembodiment, the HAP nanoparticles 112 do not allow a good crosslinkingof the polymer strands. Therefore the first polymer film produced with ahigh ratio of HAP nanoparticles 112 is very powdery and breaks veryeasily.

In operation 410, the second solution is applied to a first surface toform a first polymer film on the surface. A first weight percentage ofthe first tissue forming nanoparticles 112 to the polymer is about0.5-95%.

In certain embodiment, the first polymer film is formed by applying thesecond solution to the first surface, and allowing it to dry. In certainembodiment, the second solution can be dried at a room temperature(e.g., 25° C.). In certain embodiment, the second solution is mildlyheated to form the polymer film on the surface, for example, at atemperature higher than room temperature (e.g., 25° C.) and lower than80° C. In certain embodiment, the drying process is under a vacuumcondition. In certain embodiment, the surface is a Teflon surface. Incertain embodiment, the first surface is a polytetrafluoroethylene(PTFE) surface. In certain embodiment, the second solution can be driedon a PTFE surface under vacuum and under mild heat for less than 24hours to form the polymer film. The thickness of the polymer film can beabout 2-10 mm.

In operation 414, the first polymer film is cut into a plurality offirst strips, i.e., the first polymer layers 102.

The first layers 102 can be cut into any suitable shape and size toproduce a biocompatible structure with a predetermined shape and size.In certain embodiment, each of the first layers 102 is identical toother strips. In certain embodiment, each of the strips has a length ofabout 0.002-50 cm, a width of about 0.002-50 cm, and a thickness ofabout 0.001-50 mm.

At the same time or sequentially, multiple second strips 202 can beproduced using the material and process as disclosed in the aboveoperations 402 to 414. Specifically, as shown in the operation 402, asecond polymer 214 is dissolved in a second solvent to form a thirdsolution. As shown in the operation 406, the second tissue formingnanoparticles 212 are added to the third solution to form a fourthsolution. The second weight percentage of the second polymer 214 to thesecond tissue forming material 212 in the fourth solution is about 20:1to 2:1. In certain embodiments, the ratio of the second polymer 214 tothe second tissue forming material 212 can be adjusted to meetrequirement of the condition of a patient, including the bone or muscleimplant position, size, and metabolic rate of the patient. As shown inthe operation 410, the fourth solution is applied to a second surface toform a second polymer film on the second surface. A second weightpercentage of the second tissue forming material to the polymer is about0.5-95%. As shown in the operation 414,the second polymer film is cutinto a plurality of second strips, i.e., the second polymer layers 202.

In certain embodiments, the second nanoparticles 212 can be the same asor different from the first nanoparticles 112. In certain embodiments,the second polymer 214 can be the same as or different from the firstpolymer 114. In certain embodiments, the second solvent can be the sameas or different from the first solvent. In certain embodiments, thesecond surface can be the same as or different from the first surface.In certain embodiment, the second surface is the first surface. Incertain embodiment, the second weight percentage is different from thefirst weight percentage, such that the first layers 102 is harder thanthe second strips 202, that is, the density of the first layers 102 isgreater than the density of the second strips 202. In certainembodiment, both the first tissue forming nanoparticles 112 and thesecond tissue forming nanoparticles 212 are HAP nanoparticles. In otherembodiments, at least one of the first tissue forming nanoparticles 112,the first polymer 114, the first solvent, and the first weightpercentage is different from the corresponding second tissue formingnanoparticles 212, second polymer 214, second solvent, and second weightpercentage. In certain embodiments, the second tissue formingnanoparticles 212 are polymeric nanoparticles or nanofibers.

As shown in FIG. 4B, the biocompatible structure 90 is formed bystacking the first layers 102, the first bone particle layers 106, thesecond strips 202, and the second bone particle layers 206. Then thestructure is coated by a coating 300 formed from a fifth solution, andthe third bone particles 316 are then added onto the surface of thecoating 300. The fifth solution can be the same or different from thesecond solution and/or the fourth solution.

Only three first polymer layers 102-1, 102-2, and 102-3 and three secondpolymer layers 202-1, 202-2, 202-3 are shown in FIG. 4B. However, asshown in FIG. 2B, the number of the first polymer layers 102 can be m,and the number of the second polymer layers can be n, where m and n arepositive integers.

In certain embodiments, as shown in operation 418, the first polymerlayer 102-1 is disposed on a surface, the first spacer layer 106-1 isstacked on the first polymer layer 102-1, the first polymer layer 102-2is stacked on the first spacer layer 106-2, the first spacer layer 106-2is stacked on the first polymer layer 102-2, the first polymer layer102-3 is stacked on the first spacer layer 106-2, and the first spacerlayer 106-3 is stacked on the first polymer layer 102-3. Byalternatively disposing first polymer layers 102 and first spacer layers106, the first base structure 100 with a predetermined shape and size isconstructed. In certain embodiments, at least one first polymer layer102 is located as one of the outside layers of the first base structure100. In certain embodiment, at least one first spacer layer 106 islocated as one of the outside layers of the first base structure 100.

In certain embodiments, as shown in operation 422, the second polymerlayer 202-1 is disposed on the first spacer layer 106-3, the secondspacer layer 206-1 is stacked on the second polymer layer 202-1, thesecond polymer layer 202-2 is stacked on the second spacer layer 206-1,the second spacer layer 206-2 is stacked on the second polymer layer202-2, and the second polymer layer 202-3 is stacked on the secondspacer layer 206-2. By alternatively disposing second polymer layers 202and second spacer layers 206, the second base structure 200 with apredetermined shape and size is constructed. In certain embodiments, apolymer layer 202 is located as the most outside layer of the secondbase structure 200. In certain embodiment, a second spacer layer 206 islocated as one of the most outside layer of the second base structure200. In certain embodiments, a second polymer layer 202 is located asthe most inner side layer adjacent to the first base structure 100. Incertain embodiment, a second spacer layer 206 is located as the mostinner side layer adjacent to the first base structure. Thus theinterface between the first base structure 100 and the second basestructure 200 can be a first polymer layer 102-second polymer layer 202interface, a first polymer layer 102-second spacer particle layer 206interface, a first spacer layer 106-second polymer layer 202 interface,or a first spacer layer 106-second spacer layer 206 interface.

In certain embodiments, as shown in FIG. 4B, the first base structure100 and the second base structure 200 are formed in one step of theoperations 418 and 422 by stacking the first polymer layers 102 and thefirst spacer layers 106 alternately, and stacking the second polymerlayers 202 and the second spacer layers 106 alternately on thealternately disposed first polymer layers 102 and the first spacerlayers 106.

The operation 422 can further include liquefying the stacked first basestructure 100 and the second base structure 200. In order for the entirestructure to stay together, methanol or other solvent of the polymer isadded by, for example pipetting, to superficially liquefy the polymerlayers 102 and 202, such that the spacer particles 116 and 226 can be“trapped” in the polymer layers 102 and 202 when the structure dries.The spacer particles 116 and 216 can be partially embedded in thepolymer layers 102 and 202. After the polymer layers 102 and 202re-solidifies, the bone particle layers 106 and 206 are connected withthe polymer layers 102 and 202.

In this embodiment, the first base structure 100 and the second basestructure 200 are liquefied in one operation. In certain embodiments,the liquefying solution can be methanol or any other solvent, the firstsolution, the second solution, the third solution, the fourth solution,or any other solution that can liquefy the base structures. In certainembodiments, the first base structure 100 and the second base structure200 can be liquefied using the same solution or different solutions. Incertain embodiments, the first base structure 100 and the second basestructure 200 are produced separately, liquefied separately, driedseparately, and then stacked together.

In certain embodiments, when a biocompatible structure having more thantwo base structures is needed, then the above process includes stackingmore than two, for example, 3, 4, 5, 6 or more base structures together.

In operation 426, a fifth solution is applied to the stacked structureof the first base structure 100 and the second structure 200 to form acoated structure. In certain embodiments, the fifth solution is thesecond solution or the fourth solution. In certain embodiment, theweight percentage of the tissue forming nanoparticles in the fifthsolution is between the first weight percentage of the tissue formingnanoparticles in the second solution and the second weight percentage ofthe tissue forming nanoparticles in the fourth solution. In certainembodiments, the stacked structure built as described above is thencoated by covering with a polymer film that is in a liquid form. Incertain embodiment, the fifth solution is a sticky solution beforeapplying to the stacked structure. In certain embodiment, part of thefifth solution poured on the surface of the stacked structure penetratesto the inside of the stacked structure. The poured fifth solution formsa coat 300 on the surface of the stacked structure and helps to hold thecomponents of the stacked structure together.

In certain embodiment, the operation 426 further includes adding thethird spacer particles 316 to the coated structure to form thebiocompatible structure 90. In certain embodiment, the third spacerparticles 316 can be nano-sized bone particles, micro-sized boneparticles, or a mixture thereof. The structure is then allowed to dryovernight under vacuum and mild heat to form the biocompatible structure90 according to the present disclosure.

The biocompatible structure 90 can be any shape and size such that thebiocompatible structure 90 matches the size of the bone defect thatneeds to be regenerated. In certain embodiment, the biocompatiblestructure 90 has a cylindrical shape or a spherical shape. In certainembodiment, the length of the biocompatible structure 90 is about 2.5 cm(1 inch) and the diameter is about 0.1-1 cm, which matches the diameterof the bone that needs to be replaced.

In certain embodiment, the method further includes subjecting thebiocompatible structure 90 having one or more base structures to plasmatreatment. For example, once completely dried, the biocompatiblestructure 90 is placed into glass vials for storage. The biocompatiblestructure 90 is plasma treated by a radio frequency (RF) plasmadischarge device, under an environment of oxygen, nitrogen or a mixtureof oxygen and nitrogen. In certain embodiment, the RF plasma treatmenttime is about 10-30 minutes.

In certain embodiment, the RF plasma treatment time is about 5-15minutes. In certain embodiment, the RF plasma treatment time is about1-3 minutes. In certain embodiment, the plasma treated biocompatiblestructure 90 is sterilized and sent for animal studies. The purpose ofthe plasma treatment is to break the surface bonds of the polymer. Afterplasma treatment, oxygen atoms “attach” to the surface, changing thesurface energy of the surface such that the surface becomes morehydrophilic and has oxygen and nitrogen rich functional groups.

In certain embodiment, the method of manufacturing the biocompatiblestructure 90 further includes adding a third tissue forming material 326to the biocompatible structure 90. In certain embodiment, the thirdtissue forming material 326 includes a bioactive material, cells, or amixture thereof. The bioactive material includes proteins, enzymes,growth factors, amino acids, bone morphogenic proteins, platelet derivedgrowth factors, vascular endothelial growth factors, or a mixturethereof. The cells includes epithelial cells, neurons, glial cells,astrocytes, podocytes, mammary epithelial cells, islet cells,endothelial cells, mesenchymal cells, stem cells, osteoblast, musclecells, striated muscle cells, fibroblasts, hepatocytes, ligamentfibroblasts, tendon fibroblasts, chondrocytes, or a mixture thereof. Incertain embodiments, the third tissue forming material 326 located inthe part of the surface of the biocompatible structure 90 correspondingto the first base structure 100 is different from the third tissueforming material 326 located in the part of the surface of thebiocompatible structure 90 corresponding to the second base structure200.

In other embodiments, as shown in FIG. 5, the first base structure 100and the second base structure 200 can be formed independently on thesame or separated surfaces, and then stacked the first base structure100 and the second base structure afterwards, coating the stackedstructure, and optionally plasma treating to form the biocompatiblestructure.

Alternatively, as shown in FIG. 6, the first base structure 100 can becoated and optionally treated to form a first biocompatiblesub-structure. The second base structure 100 can be coated andoptionally plasma treated for form a second biocompatible structure. Thefirst biocompatible sub-structure and the second biocompatiblesub-structure are then stacked together, coated, and optionally plasmatreated to form the biocompatible structure. Alternatively, thecombination of the coated, dried and optionally plasma treated firstbiocompatible sub-structure and second biocompatible sub-structure canbe performed, instead of another coating process, by binding through anorganic binder, or by any other means such that the first biocompatiblesub-structure and the second biocompatible sub-structure are stablelycombined as one unity.

In certain embodiment, instead of manufacturing the biocompatiblestructure 90 and then using it as implant material, the biocompatiblestructures 90 can also be formed in situ. For example, a first polymerlayer is air sprayed at an implant site or a bone defect area, a firstlayer of bone particles is then added to the polymer layer and depositson the polymer layer. After that, a second polymer layer is air sprayedon the first bone particle layer, followed by adding a second layer ofbone particles. The process is repeated until the biocompatiblestructure, including alternating polymer layers and bone particlelayers, matches the implant site or mimics the bone defect that needs tobe replaced. The biocompatible structure 90 formed in situ can alsoinclude one or more base structures. For example, a series ofalternatively stacked first polymer layer and first bone particle layeris formed first, corresponding to a bone area 500; then a series ofalternatively stacked first polymer layer and first bone particle layeris formed first, corresponding to a muscle area 600.

In certain embodiment, a Doctor of Medicine (MD) can take a 3D computeraxial tomography scan (CAT) of a patient and sent the result for exampleby emailing the CAT scan file to a manufacturer. The manufacturer thencan build the implant according to the present disclosure to perfectlymatch the actual bone defect.

One example is provided according to the process shown in FIG. 4A andFIG. 4B.

In operation 402, 500 ml methanol is added to a 1 L beaker. The beakeris placed on a magnetic stirrer and a magnetic stir bar is used formixing. 80 grams polyurethane 114 is then added to the methanol in thebeaker. The solution is mixed by the stirring bar to completely dissolvethe polyurethane in the methanol solvent and uniformly distributed thepolyurethane 114 in the solution. The mixing and dissolving ofpolyurethane is at room temperature. In certain embodiment, the solutioncan be heated to accelerate the process.

In operation 406, 20 gram HAP nanoparticles 112 (e.g., Berkeley AdvancedBiomaterials, Inc.) is then added to the solution. Sonication is appliedto guarantee the evenly distribution of the HAP nanoparticles 112 in thesolution.

In operation 410, 10 ml of the solution is pipetted from the beaker andapplied to a PTFE surface. A thin layer of solution is formed on thePTEF surface. The thin layer of solution is allowed to dry at roomtemperature for variable times to form a polymer film. Alternatively,the layer of solution on the PTFE surface can be placed in an oven toheat or low pressure for a period of time to accelerate the formation ofthe polymer film. In certain embodiment, the temperature can be about30-70° C., and the period of time for the heating is about 2-1500minutes. In certain embodiment, the second solution is allowed to dry ona PTFE surface under vacuum under mild heat for less than 24 hours toform the polymer film. The thickness of the polymer film can be about0.01-50 mm.

In operation 414, the polymer film is then cut into identical stripswith a length of about 0.05-20 cm, a width of about 0.02-5 cm, and athickness of about 0.01-50 mm. In certain embodiment, the polymer filmcan be cut into strips with varies shape and size. Those strips arefirst polymer layers 102.

The operations 402, 406, 410 and 414 can be used to prepare the firstplurality of layers 102. In the same matter, the operations 402, 406,410 and 414 can be used to prepare the second polymer layers 202. Theweight percentage of HAP nanoparticles in the total weight of the firstpolymer layers 102 is different from that in the second polymer layers202. In one embodiment, the first weight percentage of HAP nanoparticlesin the total weight of the first polymer layers 102 is about 15-30%. Inone embodiment, the first weight percentage of HAP nanoparticles in thetotal weight of the first polymer layers 102 is about 17-23%. In oneembodiment, the first weight percentage of HAP nanoparticles in thetotal weight of the first polymer layers 102 is about 20%. In oneembodiment, the second weight percentage of HAP nanoparticles in thetotal weight of the second polymer layers 202 is about 10-25%. In oneembodiment, the second weight percentage of HAP nanoparticles in thetotal weight of the second polymer layers 202 is about 15-20%. In oneembodiment, the second weight percentage of HAP nanoparticles in thetotal weight of the second polymer layers 202 is about 18%.

In certain embodiments, the first weight percentage is greater than thesecond weight percentage. In certain embodiments, the first weightpercentage is 0.1-50% greater than the second weight percentage. Incertain embodiments, the first weight percentage is 0.5-10% greater thanthe second weight percentage. In certain embodiments, the first weightpercentage is 1-5% greater than the second weight percentage. In certainembodiments, the first weight percentage is 2% greater than the secondweight percentage.

In certain embodiments, as shown in operation 418, the first polymerlayer 102-1, the first spacer layer 106-1, the first polymer layer102-2, the first spacer layer 106-2, the first polymer layer 102-3, thefirst spacer layer 106-3 . . . the first spacer layer 106-m, the secondpolymer layer 202-1, the second spacer layer 206-1, the second polymerlayer 202-2, the second spacer layer 206-2, the second polymer layer202-3 . . . the second polymer layer 202-n are stacked to form a threedimensional structure.

In this example, the spacer particles 116 of the first spacer layers 106and the spacer particles 216 of the second spacer layers 206 are boneparticles. In certain embodiments, the bone particle density and thethickness of the first bone particles 116 are different from those ofthe second bone particles 216. In certain embodiments, the density ofthe first bone particles 116 is greater than the density of the boneparticles 216.

After stacking of the three dimensional structure, in order for theentire structure to stay together, methanol or other solvent of thepolymer is added by, for example pipetting, to superficially liquefy thepolymer layers 102 and 202, such that the bone particles 116 and 206 canbe “trapped” in the polymer layers 102 and 202 when the structure dries.The bone particles 116 and 216 can be partially embedded in the polymerlayers 102 and 202. After the polymer layers 102 and 202 re-solidifies,the bone particle layers 106 and 206 are connected with the polymerlayers 102 and 202. Alternatively, the liquefying step can be performedtwo or more times during the stacking of the three dimensionalstructure.

In operation 426, a certain volume, for example 1 ml, of themethanol/polyurethane/HAP nanoparticle solution is added to the surfaceof the three-dimensional structure and allowed to dry. In oneembodiment, the methanol/polyurethane/HAP nanoparticle solution is thesecond solution or the fourth solution. Accordingly, a coating 300 isformed on the surface of the three-dimensional structure to form acoated structure. In certain embodiment, the coating 300 not only coversthe outside of the three-dimensional structure, but also can penetrateto the inside of the three-dimensional structure.

Further, a third spacer particles 316, which could be the same as thefirst bone particles 116 and second bone particles 216, or othersuitable particles, may be added to the surface of the coating 300.

In certain embodiment, the coated structure is then dried under vacuumovernight. In certain embodiment, the structure is further subjected toplasma treatment to form the biocompatible structure 90. The plasmatreatment may be a nitrogen or oxygen plasma treatment.

In certain embodiment, the first base structure 100 and the second basestructure 200 of the biocompatible structure 90 are configured for theregeneration of two different portions of a bone loss/implant site,where the first base structure 100 corresponds to a hard portion of thebone loss and the second base structure 200 corresponds to a softerportion of the bone loss.

One example is provided according to the process shown in FIG. 4A andFIG. 4B. In operation 402, 500 ml methanol is added to a 1L beaker. Thebeaker is placed on a magnetic stirrer and a magnetic stir bar is usedfor mixing. 80 grams polyurethane 114 is then added to the methanol inthe beaker. The solution is mixed by the stirring bar to completelydissolve the polyurethane in the methanol solvent and uniformlydistributed the polyurethane 114 in the solution. The mixing anddissolving of polyurethane is at room temperature. In certainembodiment, the solution can be heated to accelerate the process.

In operation 406, 20 gram HAP nanoparticles 112 (e.g., Berkeley AdvancedBiomaterials, Inc.) is then added to the solution. Sonication is appliedto guarantee the evenly distribution of the HAP nanoparticles 112 in thesolution.

In operation 410, 10 ml of the solution is pipetted from the beaker andapplied to a PTFE surface. A thin layer of solution is formed on thePTEF surface. The thin layer of solution is allowed to dry at roomtemperature for variable times to form a polymer film. Alternatively,the layer of solution on the PTFE surface can be placed in an oven toheat or low pressure for a period of time to accelerate the formation ofthe polymer film. In certain embodiment, the temperature can be about30-70° C., and the period of time for the heating is about 2-1500minutes. In certain embodiment, the second solution is allowed to dry ona PTFE surface under vacuum under mild heat for less than 24 hours toform the polymer film. The thickness of the polymer film can be about0.01-50 mm.

In operation 414, the polymer film is then cut into identical stripswith a length of about 0.05-20 cm, a width of about 0.02-5 cm, and athickness of about 0.01-50 mm. In certain embodiment, the polymer filmcan be cut into strips with varies shape and size. Those strips arefirst polymer layers 102.

The operations 402, 406, 410 and 414 can be used to prepare the firstplurality of layers 102. In the same matter, the operations 402, 406,410 and 414 can be used to prepare the second polymer layers 202, exceptthat the second tissue forming material 212 is nanofiber or polymericnanoparticles. The weight percentage of HAP nanoparticles in the totalweight of the first polymer layers 102 is different from the nanofibersin the second polymer layers 202. In one embodiment, the first weightpercentage of HAP nanoparticles in the total weight of the first polymerlayers 102 is about 15-30%. In one embodiment, the first weightpercentage of HAP nanoparticles in the total weight of the first polymerlayers 102 is about 17-23%. In one embodiment, the first weightpercentage of HAP nanoparticles in the total weight of the first polymerlayers 102 is about 20%. In one embodiment, the second weight percentageof nanofibers in the total weight of the second polymer layers 202 isabout 10-25%. In one embodiment, the second weight percentage ofnanofibers in the total weight of the second polymer layers 202 is about15-20%. In one embodiment, the second weight percentage of nanofibers inthe total weight of the second polymer layers 202 is about 18%. Incertain embodiments, the first weight percentage is greater than thesecond weight percentage. In certain embodiments, the first weightpercentage is 0.1-50% greater than the second weight percentage. Incertain embodiments, the first weight percentage is 0.5-10% greater thanthe second weight percentage. In certain embodiments, the first weightpercentage is 1-5% greater than the second weight percentage. In certainembodiments, the first weight percentage is 2% greater than the secondweight percentage. In certain embodiments, as shown in operation 418,the first polymer layer 102-1, the first spacer layer 106-1, the firstpolymer layer 102-2, the first spacer layer 106-2, the first polymerlayer 102-3, the first spacer layer 106-3 . . . the first spacer layer106-m, the second polymer layer 202-1, the second spacer layer 206-1,the second polymer layer 202-2, the second spacer layer 206-2, thesecond polymer layer 202-3 . . . the second polymer layer 202-n arestacked to form a three dimensional structure.

In this example, the spacer particles 116 of the first spacer layers 106are bone particles and the spacer particles 216 of the second spacerlayers 206 are nanofibers or polymeric nanoparticles. In certainembodiments, the bone particle density and the thickness of the firstbone particles 116 are different from those of the nanofibers orpolymeric nanoparticles 216. In certain embodiments, the density of thefirst bone particles 116 is greater than the density of the nanofibersor polymeric nanoparticles 216.

After stacking of the three dimensional structure, in order for theentire structure to stay together, methanol or other solvent of thepolymer is added by, for example pipetting, to superficially liquefy thepolymer layers 102 and 202, such that the bone particles 116 and thenanofibers or polymeric nanoparticles 216 can be “trapped” in thepolymer layers 102 and 202 when the structure dries. The bone particles116 and the nanofibers 216 can be partially embedded in the polymerlayers 102 and 202. After the polymer layers 102 and 202 re-solidifies,the bone particle layers 106 and nanofiber layer or polymericnanoparticle layer 206 are connected with the polymer layers 102 and202. Alternatively, the liquefying step can be performed two or moretimes during the stacking of the three dimensional structure.

In operation 426, a certain volume, for example 1 ml, of themethanol/polyurethane/HAP nanoparticle solution ormethanol/polyurethane/nanofiber solution is added to the surface of thethree-dimensional structure and allowed to dry. In one embodiment, themethanol/polyurethane/HAP nanoparticle solutionmethanol/polyurethane/nanofiber solution is the second solution or thefourth solution. Accordingly, a coating 300 is formed on the surface ofthe three-dimensional structure to form a coated structure. In certainembodiment, the coating 300 not only covers the outside of thethree-dimensional structure, but also can penetrate to the inside of thethree-dimensional structure.

Further, a third spacer particles 316, which could be the same as thefirst bone particles 116 or the second nanofibers or polymericnanoparticles 216, or other suitable particles, may be added to thesurface of the coating 300.

In certain embodiment, the coated structure is then dried under vacuumovernight. In certain embodiment, the structure is further subjected toplasma treatment to form the biocompatible structure 90.

In certain embodiment, the first base structure 100 and the second basestructure 200 of the biocompatible structure 90 are configured for theregeneration of an implant site having bone loss and muscle loss. Thefirst base structure 100 corresponds to the bone loss portion of theimplant site, facilitating regeneration of bone tissue. The second basestructure 200 corresponds to the muscle loss portion of the implantsite, facilitating regeneration of muscle tissue.

In certain embodiment, the biocompatible structure 90 can have threeportions, one corresponds to a soft bone loss portion, one correspondsto a bard bone loss portion, and one corresponds to a muscle portion.

A variety of biocompatible structures 90 having one or more basestructures can be produced according to the above example. In certainembodiments, the base structures can have differentHAP/nanofiber/polymeric nanoparticle concentration in the polymer layer,where the HAP/nanofiber/polymeric nanoparticle concentration in thepolymer film is closely related with the characters of the correspondingbase structure. In certain embodiment, the base structures can havedifferent polymer layer to polymer layer distance. In certainembodiment, the base structures can have different thickness of the boneparticle layer or nanofiber/polymeric nanoparticle layer. In certainembodiment, the base structures can have different particle poredensity. The HAP/nanofiber/polymeric nanoparticle concentration in thepolymer film and the thickness and density of the particles in theparticle layers are closely related with the characters of the producedbiocompatible structure.

3D printing or additive manufacturing is a process of making athree-dimensional solid object of virtually any shape from a digitalmodel. 3D printing is achieved using an additive process, wheresuccessive layers of material are laid down in different shapes. Thematerial for manufacturing the biocompatible structure of the presentdisclosure includes polymers and particles, and the biocompatiblestructure is essentially a layered structure. Thus, in certainembodiments, the biocompatible structure of the present disclosure issuitable for 3D printing. In other embodiments, the biocompatiblestructure of the present disclosure is also suitable for layer by layer2D printing

In certain embodiment, a 3D model is built for an implant surgical site.The 3D model can be created with a computer aided design package or via3D printer. The implant surgical site can be a bone and muscle surgicalsite that has bone and muscle tissue loss, a dental site that a crown isneeded or a tooth need to be replaced, a tissue or a skin area that hastissue or skin loss, or any other implant surgical site of a patientthat need an implant. The 3D model can be built based on 3D images suchas x-ray computed tomography (CT) images, magnetic resonance imaging(MRI) images, or any other methods that can aid the construction of a 3Dmodel. The 3D model can be constructed based on the shape, size,intensity, strength or other structure features of the surgical sitedirectly, or the shape, size, intensity, strength or other structurefeatures of a separated tissue such as a lost tooth, or the shape, size,intensity, strength or other structure features of a normal body portionthat is symmetrical to the implant surgical site. In certainembodiments, a 3D structure model database is used to aid theconstruction of the 3D model of the implant surgical site. The 3Dstructure model database may be generated from 3D images collected fromdifferent patients or objects, and processed by a suitable algorithm.Once the 3D model is built for the implant surgical site or for theimplant complementary to the implant surgical site, the implant can begenerated by a 3D printer.

A 3D printer is a limited type of industrial robot that is capable ofcarrying out an additive process undercomputer control. A 3D printerfrom Stratasys Inc, Hewlett-Packard Company, 3D systems Corp., the ExOneCompany, Voxeljet AG, Group Gorge, Camtek LTD., etc. can be used. Incertain embodiment, a Solidoodle, a Cubify Cube, a Stratasys Mojo, aHyrel E2 Hobbyist, or a customized RepRap 3D printer, or any othermarket available or lab built 3D printers can be used to generate theimplant of the present disclosure.

The 3D printing technology is used for both prototyping and distributedmanufacturing with applications in architecture, construction (AEC),industrial design, automotive, aerospace, military, engineering, civilengineering, dental and medical industries, biotech (human tissuereplacement), fashion, footwear, jewelry, eyewear, education, geographicinformation systems, food, and many other fields. One study has foundthat open source 3D printing could become a mass market item becausedomestic 3D printers can offset their capital costs by enablingconsumers to avoid costs associated with purchasing common householdobjects

A large number of additive processes are now available. They differ inthe way layers are deposited to create parts and in the materials thatcan be used. Some methods melt or soften material to produce the layers,e.g. selective laser melting (SLM) or direct metal laser sintering(DMLS), selective laser sintering (SLS), fused deposition modeling(FDM), while others cure liquid materials using different sophisticatedtechnologies, e.g. stereolithography (SLA). With laminated objectmanufacturing (LOM), thin layers are cut to shape and joined together(e.g. paper, polymer, metal). Each method has its own advantages anddrawbacks, and some companies consequently offer a choice between powderand polymer for the material from which the object is built.

In certain embodiment of the present disclosure, the HAP particles, thebone particles, the polymer, the solution, or the polymer film can beused as material of a 3D printer to generate the implant including alayered structure.

In certain embodiment, the entire biocompatible structures aremanufactured by 3D printing or layer by layer 2D printing, and used asthe implant. In certain embodiment, the base structures formed frompolymer strip layers and layers of tissue forming particle layersalternatively are produced by 3D printing or layer by layer 2D printing,and then assembled to generate the biocompatible structure. In certainembodiment, the polymer film is manufactured by 3D printing or layer bylayer 2D printing, and then used to generate the base structures. Incertain embodiment, a variety of cells, for example bone cells, stemcells, fibroblast cells, etc., can be seeded or printed on thebiocompatible structure, the base structure, or the polymer film.

The biocompatible structure 90 can be any shape, size and weight to fitwith an implant site. In certain embodiment, long bones were surgicallyremoved from the tibia of goats, and biocompatible structures conform tothe implant sited of the goats according to the present disclosure areused for bone regeneration of the goats.

In certain embodiment, when the biocompatible structure 90 having onebase structure 100 is used in dental applications for bone generation,the concentration of HAP nanoparticles can be much higher than theconcentration of HAP nanoparticles in the implant or the biocompatiblestructure for some other bone regeneration, for example, tibiaregeneration. In certain embodiment, the biocompatible structure 90 fordental applications can be crumbled and forms a lot of particles withhigh surface area.

FIGS. 7A and 7B show a pull test system 700 used to measure the maximumload and maximum stress of polymer films 750 with various concentrationsof polyurethane and HAP nanoparticle in accordance with certainembodiments of the present disclosure. In one example, the mechanicalbehavior of the composites was analyzed using an ADMET 7600 EXPERTsingle-column, universal, electromechanical testing machine. Theinstrument performs a “pull test” by stretching the polymer film in itsaxial direction and instantaneously produces a “csv” file using the eP2Digital Controller and Gauge Safe Basic Testing Software. The pull testsystem 700 includes a pull test structure 710, a digital controller 730and, optionally, a computer 750. The pull test structure 710 has a base711, a column 713 fixed to and perpendicular to the base 711, a bottomhead 715 connected with two bottom grips 717 a and 717 b facing eachother, a top head 721 connected with two top grips 719 a and 719 bfacing each other, a scale 723 attached to the column 713, and a rail725 placed in the column 713. At least one of the top head 721 and thebottom head 715 is connected with the rail 725 and is movable along therail 725. In this embodiment, the top head 721 is connected through achain or a cable to a motor (not shown) and the chain or the cablepulls/drives the top head 721 along the rail 725. The top grips 719 a/719 b move together and at the same speed with the top head 721.

Polymer films 750 were prepared and tested. In certain embodiment, thepolymer films 750 contain various concentrations of polyurethane and HAPnanoparticles. In one embodiment, the weight percentage of the HAPnanoparticles in the polymer films are 0%, 0.5%, 1%, 2%, 3%, 5%, 10%,15%, 20% and 30% respectively. As described above, the weight percentageof the HAP nanoparticles is defined as the weight of the HAPnanoparticle powder (in gram) used for preparing the polymer filmdivided by the total weight of HAP nanoparticle powder (in gram) andsolid polymers (in gram) used for preparing the polymer film 750. Thepolymer films 750 used in the test have predetermined dimensions. Incertain embodiments, the size of the polymer films 750 is 6 cm×1.5cm×0.02 cm. In certain embodiment, polymer films with the sameconcentration of HAP nanoparticles are prepared with different sizes fortesting.

During the maximum load and maximum stress testing process, the topgrips 721 a/ 721 b and the bottom grips 717 a/ 717 b clip two ends ofthe polymer film 750 in the longtitudial direction of the polymer film750. The dimension of the polymer film 750 and the parameters of theforce to be used are entered into the digital controller 730. In certainembodiments, the length of the polymer film used in the calculation isan effective length, for example, measured by the scale, from the bottomedges of the top grips 719 a/ 719 b to the top edges of the bottom grips717 a/ 717 b. In certain embodiments, if the polymer film 750 clippedbetween the top grips 7191/b and the bottom grips 717 a/b has a dog boneshape, the length used for calculation is the narrow portion of the dogbone shape. When the testing starts, the motor moves at least one of thetop head 721 and the bottom head 715, for example, the top head 721. Thetop grips 719 a/ 719 b move together and at the same speed with the tophead 721 to pull the polymer film 750 at a predetermined speed. Incertain embodiment, the speed can be 0.01-2.5 mm per minute. The topgrips 719 a/ 719 b move along the rail 725 at a predetermined speed topull the polymer film 750 until the polymer film 750 breaks. Theoriginal dimensions of the polymer film 750, the moving speed of the topgrips 719 a/ 719 b, the length of the polymer film 750 immediatelybefore it breaks are recorded. The maximum load and the maximum stressare calculated. In certain embodiments, the calculation is performed bya processor (not shown) in the computer 750. The maximum load is thepull force (newton) applied to the polymer film 750 when the polymerfilm breaks. The maximum stress (KPa) is the pull force applied to thepolymer film 750 when the polymer film 750 breaks divided by thecross-sectional area of the polymer film 750 (the original width timesthe original thickness of the polymer film 750).

The load and stress tests are performed for the polymer films 750 madeaccording to the present disclosure. In certain embodiments, the polymerfilms contain various concentrations of polyurethane and HAPnanoparticles.

FIG. 8 is a load graph of the polymer films 750 in a two dimensionalcoordinate system, which shows a functional relationship between theweight percentage of the HAP nanoparticles in a polymer film and amaximum load of that polymer film. The X-axis of the coordinate systemis the weight percentage of the HAP nanoparticles and the Y-axis of thecoordinate system is the maximum load of the polymer film. As shown inFIG. 8, the maximum load (in newton) for the polymer films 750containing 0%, 0.5%, 1%, 2%, 3%, 5%, 10%, 20% and 30% of HAPnanoparticles are measured and calculated. The maximum load increasessharply from about 20 newton (N) to about 44 N when the HAPconcentration increases from 0% to about 1%. Then the maximum load dropsto about 31 N when the HAP concentration increases from 1% to around10%. After that, the maximum load increases again to about 41 N ataround 20% HAP concentration and drops to about 38 N at around 30% HAPconcentration. Thus, the load graph has two peaks corresponding to 1%and around 20% of HAP concentration. In certain embodiment, the secondpeak at around 20% HAP concentration in the load graph is named loadpeak.

FIG. 9 is a stress graph of the polymer films 750 in a two dimensionalcoordinate system, which shows a functional relationship between theweight percentage of the HAP nanoparticles in a polymer film and amaximum load of that polymer film. The X-axis of the coordinate systemis the weight percentage of the HAP nanoparticles and the Y-axis of thecoordinate system is the maximum stress of the polymer film 550. Asshown in FIG. 9, the maximum stress (in KPa) for the polymer filmscontaining 0%, 0.5%, 1%, 2%, 3%, 5%, 10%, 20% and 30% of HAPnanoparticles are measured and calculated. The maximum stress increasesfrom about 11,000 KPa to about 15,000 KPa when the HAP concentrationincreases from 0% to about 1%. Then the maximum stress decreases toabout 13,600 KPa when the HAP concentration increases from 1% to about3%. After that, the maximum stress increases to about 22,000 KPa whenthe HAP concentration increases from about 3% to about 20%. Furtherincreasing HAP concentration in the polymer films from about 20% to 30%can result in decreasing of the maximum stress from 22,000 to about20,800 KPa. Thus, the stress graph has two peaks corresponding to 1% and20% of HAP concentration. In certain embodiment, the second peak at 20%HAP concentration in the stress graph is named stress peak.

In certain embodiments, a computer 750 can be used to calculate optimalweight percentage of HAP in the polymer film 750 according to the aboveload and stress graphs of a series of polymer films 750. The computer750, utilizing one or more CPUs, can receive the data from the pull teststructure 710 and the digital controller 730, run a calculationsoftware, and then present the result on a monitor.

An optimal weigh percentage of HAP in the polymer film 750 is determinedbased on the results from the load graph and the stress graph by thecomputer 730. In certain embodiments, both the load graph and the stressgraph have at least two peaks. The first peak 804 in the load graphcorresponding to a lower HAP concentration, and the second peak 808 inthe load graph corresponding to a higher HAP concentration. The firstpeak 904 in the stress graph corresponding to a lower HAP concentration,and the second peak 908 in the stress graph corresponding to a higherHAP concentration. The second peak 808 in the load graph is named loadpeak 808, and the second peak 908 in the stress graph is named stresspeak 908. The peak values from the load peak 808 and the stress peak 908are extracted. In this example, both of the load peak 808 and the stresspeak 908 correspond to a HAP weight percentage (HAP concentration) of20%. The maximum value and the minimum value of the load peak 808 andthe stress peak 708 are determined. In this example, both the maximumvalue and the minimum value are 20%. The optimal concentration range hasan upper limit value and a lower limit value.

The upper limit value is the maximum value plus a first predeterminedvalue. The lower limit value is the minimum value minus a secondpredetermined value. Each of the first predetermined value and thesecond predetermined value can be, for example, 10%, 5%, or 0%.Accordingly, in this example, the optimal concentration range of the HAPin the polymer film is 10%-30%, preferably 15%-25%, and more preferably20%.

In another example, the load peak 808 and the stress peak 908 havedifferent values. For example, the load peak may be at 17.5% and thestress peak may be at 22.5%. Accordingly, the maximum value is 22.5% andthe minimum value is 17.5%. With the first and second predeterminedvalues at about 10%, preferably 5%, and more preferably 0%, the optimalconcentration ranges of the HAP weight percentage in the polymer filmare 7.5%-32.5%, preferably 12.5%-27.5%, and more preferably 17.5%-22.5%.In other embodiments, the first and second predetermined values can bedifferent values.

In certain embodiments, according to the results shown in FIGS. 8 and 9,the polymer film with 20% HAP concentration shows good structurestability and strength.

In certain embodiments, the biocompatible structure 90 including onebase structure 100 prepared according to the present disclosure for thetreatment of animals and/or humans. In certain embodiment, long boneswere surgically removed from the tibia of goats. For generating longbones of these goats, biocompatible structures of a weight about 1.0-2.5grams (g) were used. For example, 10 implants with the weight of 2.39 g,2.34 g, 2.11 g, 1.86 g, 2.135 g, 2.18 g, 1.55 g, 2.5 g, 1.22 g, and 1.69g, respectively, were used to generate long bones for the goats withsurgically removed tibia part. For the above 10 examples, thebiocompatible structure was made by using 4.52 g of polymer(polyurethane), 0.45 g of HAP nanoparticles, and 15 g of bone particles.

The bone growth using the implant having one or more the biocompatiblestructures 100 according to embodiments of the present disclosure hasmaturity and integrity.

The foregoing description of the exemplary embodiments of the disclosurehas been presented only for the purposes of illustration and descriptionand is not intended to be exhaustive or to limit the disclosure to theprecise forms disclosed. Many modifications and variations are possiblein light of the above teaching.

The embodiments are chosen and described in order to explain theprinciples of the disclosure and their practical application so as toactivate others skilled in the art to utilize the disclosure and variousembodiments and with various modifications as are suited to theparticular use contemplated. Alternative embodiments will becomeapparent to those skilled in the art to which the present disclosurepertains without departing from its spirit and scope. Accordingly, thescope of the present disclosure is defined by the appended claims ratherthan the foregoing description and the exemplary embodiments describedtherein.

What is claimed is:
 1. A method of producing a biocompatible structurefor bone and tissue regeneration, comprising: forming a plurality offirst polymer layers by: dissolving a first polymer in a first solventto form a first solution; adding first tissue forming nanoparticles tothe first solution to form a second solution, wherein a first weightpercentage of the first tissue forming nanoparticles to the firstpolymer is about 0.01-95%; applying the second solution to a firstsurface to form a first polymer film on the first surface, wherein thefirst tissue forming nanoparticles are dispersed in the first polymerfilm; and dividing the first polymer film into the plurality of firstpolymer layers; forming a plurality of second polymer layers by:dissolving a second polymer in a second solvent to form a thirdsolution; adding second tissue forming nanoparticles to the thirdsolution to form a fourth solution, wherein a second weight percentageof the second tissue forming nanoparticles to the second polymer isgreater than the first weight percentage; applying the fourth solutionto a second surface to form a second polymer film on the second surface,wherein the second tissue forming nanoparticles are dispersed in thesecond polymer film; and dividing the second polymer film into theplurality of second polymer layers; and forming the biocompatiblestructure by the first polymer layers, first spacer particles, thesecond polymer layers, second spacer particles, and a fifth solution,wherein the biocompatible structure includes the first polymer layers;the second polymer layers; the first spacer particles placed between twoof the first polymer layers; and the second spacer particles placedbetween two of the second polymer layers; and wherein the fifth solutionincludes at least one of the first and the second tissue formingparticles; at least one of the first polymer and the second polymer; andat least one of the first solvent and the second solvent.
 2. The methodof claim 1, wherein the step of forming the plurality of first polymerlayers further comprises: stirring the first solution to uniformlydistribute the first polymer in the first solution; sonicating thesecond solution to uniformly distribute the first polymer and the firsttissue forming nanoparticles in the second solution; and drying thesecond solution on the first surface to form the first polymer film onthe first surface; and wherein the step of forming the plurality ofsecond polymer layers further comprises: stirring the third solution touniformly distribute the second polymer in the third solution;sonicating the fourth solution to uniformly distribute the secondpolymer and the second tissue forming nanoparticles in the fourthsolution; and drying the fourth solution on the second surface to formthe second polymer film on the second surface.
 3. The method of claim 1,wherein the step of forming the biocompatible structure comprises:constructing a first base structure by stacking the first polymer layersand first spacer layers alternatively, wherein each of the first spacerlayers is formed by the first spacer particles; constructing a secondbase structure on the first base structure by stacking the secondpolymer layers and second spacer layers alternatively, wherein each ofthe second spacer layers is formed by the second spacer particles;applying the fifth solution to the first base structure and the secondbase structure to form a coated structure; and adding third spacerparticles to the coated structure to form the biocompatible structure.4. The method of claim 3, after adding the third spacer particles to thecoated structure, further comprising plasma treating the coatedstructure.
 5. The method of claim 3, wherein at least one of the firstpolymer layers, the second polymer layers, the first base structure, thesecond base structure, and the biocompatible structure is manufacturedby 3D printing or layer by layer 2D printing.
 6. The method of claim 3,wherein at least one of a thickness of the first polymer layer, adistance between two neighboring first polymer layers, a thickness ofthe first spacer layer, a porosity of the first spacer particles isdifferent from a thickness of the second polymer layer, a distancebetween two neighboring second polymer layers, a thickness of the firstspacer layer, a porosity of the second spacer particles, respectively,such that when being applied to an implant site, each of the first andthe second base structure corresponds to a type of tissue in the implantsite, and facilitates regeneration of the corresponding tissue.
 7. Themethod of claim 3, wherein a degradation rate of the first basestructure is slower than a degradation rage of the second basestructure.
 8. The method of claim 3, wherein each of the first and thesecond base structures has a size and shape conforming to a size andshape of corresponding tissue of an implant site.
 9. The method of claim1, wherein the first polymer is the same as the second polymer, thefirst tissue forming nanoparticles are different from the second tissueforming nanoparticles, the first solvent is the same as the secondsolvent, the first weight percentage is about 15-30%, and the secondweight percentage is about 10-25%.
 10. The method of claim 1, whereinthe first polymer is the same as the second polymer, the first tissueforming nanoparticles are the same as the second tissue formingnanoparticles, the first solvent is the same as the second solvent, thefirst weight percentage is about 15-30%, and the second weightpercentage is about 10-25%.
 11. The method of claim 10, wherein thefirst weight percentage is about 17-23%, and the second weightpercentage is about 15-20%.
 12. The method of claim 11, wherein thefirst weight percentage is about 25%, and the second weight percentageis about 22%.
 13. The method of claim 1, wherein each of the first andsecond polymer comprises a synthetic biodegradable polymer, abiodegradable polymer derived from natural source, or a mixture thereof;wherein the synthetic biodegradable polymer comprises polyurethane,polylactide (PLA), polyglycolide (PGA), poly(lactide-co-glycolide)(PLGA), poly(e-caprolactone), polydioxanone, polyanhydride, trimethylenecarbonate, poly(β-hydroxybutyrate), poly(g-ethyl glutamate), poly(DTHiminocarbonate), poly(bisphenol A iminocarbonate), poly(ortho ester),polycyanoacrylate, polyphosphazene, or a mixture thereof; and whereinthe biodegradable polymer derived from natural source comprises modifiedpolysaccharides, modified proteins, or a mixture thereof; wherein eachof the first and second tissue forming nanoparticles comprisesnanoparticles of hydroxypatites, tricalcium phosphates, mixed calciumphosphates and calcium carbonate, bone particles of zenograft, boneparticles of allografts, bone particles of autografts, bone particles ofalloplastic grafts, polymeric nanoparticles, nanofibers, or a mixturethereof; the surface is a polytetrafluoroethylene (PTFE) surface; andthe second tissue forming particles comprises nano-sized bone particles,micro-sized bone particles, or a mixture thereof.
 14. The method ofclaim 1, further comprising adding a third tissue forming material tothe biocompatible structure, wherein the third tissue forming materialcomprises a bioactive material, cells, or a mixture thereof; wherein thebioactive material comprises proteins, enzymes, growth factors, aminoacids, bone morphogenic proteins, platelet derived growth factors,vascular endothelial growth factors, or a mixture thereof; and whereinthe cells comprises epithelial cells, neurons, glial cells, astrocytes,podocytes, mammary epithelial cells, islet cells, endothelial cells,mesenchymal cells, stem cells, osteoblast, muscle cells, striated musclecells, fibroblasts, hepatocytes, ligament fibroblasts, tendonfibroblasts, chondrocytes, or a mixture thereof.
 15. The method of claim1, wherein at least one of the first polymer layers and the secondpolymer layers has a length of about 0.005-50 centimeter, a width ofabout 0.002-50 centimeter, and a thickness of about 0.001-500millimeter, and each of the first base structure and the second basestructure is in a cylindrical shape or a spherical shape.
 16. A methodof producing a biocompatible structure for bone and tissue regeneration,wherein the biocompatible structure comprises a first base structure anda second base structure each having a plurality of polymeric layers anda plurality of demineralized bone component particle layers, and acoating covering the first base structure and the second base structure;and wherein the method comprises: depositing each of the polymericlayers by air spray deposition, electrospray, droplet by dropletdeposition, 2D printing, or 3D printing of a first solution comprising apolymer and a solvent; and depositing each of the demineralized bonecomponent particle layers by electrostatic deposition or air spray of asecond solution comprising demineralized bone component particles andthe solvent.